Endoscopic methods and devices for transnasal procedures

ABSTRACT

Medical devices, systems and methods that are useable to facilitate transnasal insertion and positioning of guidewires and various other devices and instruments at desired locations within the ear, nose, throat, paranasal sinuses or cranium. Direct viewing of such placements via an endoscope.

CROSS-REFERENCE

This application is a continuation-in-part of co-pending U.S.application Ser. No. 11/725,151, filed Mar. 15, 2007. which is acontinuation-in-part of co-pending U.S. application Ser. No. 11/647,530,filed Dec. 27, 2006, which is a continuation-in-part of U.S. patentapplication Ser. No. 11/522,497, filed Sep. 15, 2006, and is also acontinuation-in-part of U.S. patent application Ser. No. 11/193,020filed Jul. 29, 2005, which is a continuation-in-part of U.S. patentapplication Ser. Nos. 10/829,917 filed Apr. 21, 2004, 10/944,270 filedSep. 17, 2004, 11/116,118 filed Apr. 26, 2005 and 11/150,847 filed Jun.10, 2005, each such application being expressly incorporated herein, inits entirety, by reference thereto, and each of which we claim priorityto under 35 USC §120.

This application also claims the benefit of U.S. Provisional ApplicationNo. 60/844,874, filed Sep. 15, 2006, which application is expresslyincorporated herein, in its entirety, by reference thereto and to whichwe claim priority under 35 USC §119.

FIELD OF THE INVENTION

The present invention relates generally to medical apparatus and methodsand more particularly to devices and methods that are useable tofacilitate transnasal insertion and positioning of guidewires andvarious other apparatus at desired locations within the ear, nose,throat, paranasal sinuses or cranium.

BACKGROUND OF THE INVENTION

Functional endoscopic sinus surgery (FESS) is currently the most commontype of surgery used to treat chronic sinusitis. In a typical FESSprocedure, an endoscope is inserted into the nostril along with one ormore surgical instruments. The surgical instruments are then used to cuttissue and/or bone, cauterize, suction, etc. In most FESS procedures,the natural ostium (e.g., opening) of at least one paranasal sinus issurgically enlarged to improve drainage from the sinus cavity. Theendoscope provides a direct line-of-sight view whereby the surgeon istypically able to visualize some but not all anatomical structureswithin the surgical field. Under visualization through the endoscope,the surgeon may remove diseased or hypertrophic tissue or bone and mayenlarge the ostia of the sinuses to restore normal drainage of thesinuses. FESS procedures can be effective in the treatment of sinusitisand for the removal of tumors, polyps and other aberrant growths fromthe nose.

The surgical instruments used in the prior art FESS procedures haveincluded; applicators, chisels, curettes, elevators, forceps, gouges,hooks, knives, saws, mallets, morselizers, needle holders, osteotomes,ostium seekers, probes, punches, backbiters, rasps, retractors,rongeurs, scissors, snares, specula, suction cannulae and trocars. Themajority of such instruments are of substantially rigid design.

In order to adequately view the operative field through the endoscopeand/or to allow insertion and use of rigid instruments, many FESSprocedures of the prior art have included the surgical removal ormodification of normal anatomical structures. For example, in many priorart FESS procedures, a total uncinectomy (e.g., removal of the uncinateprocess) is performed at the beginning of the procedure to allowvisualization of and access to the maxillary sinus ostium and/or ethmoidbulla and to permit the subsequent insertion of the rigid surgicalinstruments. Indeed, in most traditional FESS procedures, if theuncinate process is allowed to remain, such can interfere withendoscopic visualization of the maxillary sinus ostium and ethmoidbulla, as well as subsequent dissection of deep structures using theavailable rigid instrumentation.

More recently, new devices, systems and methods have been devised toenable the performance of FESS procedures and other ENT surgeries withminimal or no removal or modification of normal anatomical structures.Such new methods include, but are not limited to, uncinate-sparingprocedures using Balloon Sinuplasty™ tools and uncinate-sparingethmoidectomy procedures using catheters, non-rigid instruments andadvanced imaging techniques (Acclarent, Inc., Menlo Park, Calif.).Examples of these new devices, systems and methods are described inincorporated U.S. patent application Ser. Nos. 10/829,917 entitledDevices, Systems and Methods for Diagnosing and Treating Sinusitis andOther Disorders of the Ears, Nose and/or Throat; 10/944,270 entitledApparatus and Methods for Dilating and Modifying Ostia of ParanasalSinuses and Other Intranasal or Paranasal Structures; 11/116,118entitled Methods and Devices for Performing Procedures Within the Ear,Nose, Throat and Paranasal Sinuses filed Apr. 26, 2005 and 11/150,847filed Jun. 10, 2005, each of which is hereby incorporated herein, in itsentirety. Procedures using Balloon Sinuplasty™ tools such as thosedescribed in the above-noted applications, for example, are performableusing various types of guidance including but not limited to C-armfluoroscopy, transnasal endoscopy, optical image guidance and/orelectromagnetic image guidance.

In FESS procedures, the surgeon typically holds or navigates theendoscope with one hand while using the other hand to handle thesurgical instruments. Recognizing the desirability of integrating anendoscope with an operative device so that both could be moved with asingle hand, application Ser. No. 11/234,395 filed Sep. 23, 2005describes a number of transnasally insertable sinus guides that haveendoscopes attached thereto or integrated therewith.

There remains a need for further development of new devices andmethodology to facilitate the integration of endoscopes with sinusguides and/or other instruments to facilitate endoscopic viewing ofguidewires and/or other devices/instruments as they are transnasallyinserted, positioned and used to treat disorders of the ear, nose,throat, paranasal sinuses or other intracranial disorders that aretransnasally accessible.

SUMMARY OF THE INVENTION

A beneficial aspect of the present invention is to allow a user to beable to see an adjustable view, with an endoscope, that is generallyaligned with the same axis of movement of the user's working device.This is particularly useful when the axis of movement is at an anglewith respect to the axis of entry into the patient. This aspect allowsthe user to see “around the corner” of anatomy that ordinarily wouldblock his/her view and which would therefore require removal in atraditional FESS procedure to allow visualization. This aspect of theinvention allows the user to also verify the location of his/her BalloonSinuplasty™ tools without having to use fluoroscopy or image guidancesystems, so that the procedure does not have to be performed in anoperating room. Another beneficial aspect of the present invention isthat it enables a reduction in the amount of fluoroscopy that needs tobe performed by the user doing the procedure, resulting in a reductionin radiation exposure to the user and the patient.

Another beneficial aspect of the present invention is that it allows auser to hold a tool with an endoscope attached or incorporated therein,such that both can be held with one hand while allowing the user tomanipulate another tool with the other hand, thereby eliminating theneed for an assistant.

A method for positioning a guide device useful for delivering at leastone working device therethrough to deliver a working end portion thereofto a desired location within the ear, nose, throat or cranium of a humanor animal patient is provided, including the steps of: inserting anendoscope into or through an endoscope channel of the guide device thatincludes an elongated shaft; inserting the guide device into an internalspace of the patient; and viewing through the endoscope to guidepositioning and delivery of the guide device to an intended location inthe patient.

A method for locating a sinus ostium is provided, including the stepsof: inserting an endoscope through a nostril of a patient and advancingthe endoscope toward a location of the sinus ostium; inserting aguidewire through the nostril and advancing a distal end portion of theguidewire distally of a distal end of the endoscope; and viewing,through the endoscope, the advancement of the distal end portion of theguidewire to facilitate guidance of the advancement of the guidewirealong a desired path.

A method for treating a patient is provided, including the steps of:inserting an endoscope into or through an endoscope channel of a guidedevice that includes an elongated shaft; inserting the guide devicethrough a nostril of the patient; advancing a distal end portion of theguide device toward a sinus ostium of the patient; advancing a distalend portion of the endoscope distally of the distal end portion of theguide device, and navigating the distal end portion of the endoscopethrough the sinus ostium, said navigating being assisted byvisualization through the endoscope.

A method of visually inspecting a sinus cavity is provided, includingthe steps of: inserting an endoscope through a lumen of a working devicehaving previously been inserted through a nostril of a patient, througha sinus ostium and into the sinus cavity; and viewing the sinus cavitythrough the endoscope.

A method of directing a guidewire to a target location within the ear,nose, throat or cranium of a patient is provided, including the stepsof: inserting an illuminating guidewire internally of the patient;emitting light from a distal end portion of the guidewire; and trackingmovements of the distal end portion of the guidewire by trackingmovements of an illumination spot visible externally of the patient,wherein movements of the illumination spot correspond to movements ofthe distal end portion of the guidewire internally of the patient.

A guide device useable to position a working device at a desiredlocation within the ear, nose, throat or cranium of a human or animalsubject is provided, including: a transnasally insertable elongate shafthaving a proximal end and a distal end; a first channel into which anendoscope may be inserted so that the endoscope may be used to view atleast an area beyond the distal end of the shaft; and a second channelthrough which the working device may be advanced, wherein the firstchannel is statically located relative to the second channel.

A flexible microendoscope is provided, including: an elongated shaft; aplurality of image fibers; a lens attached at distal end of said imagefibers; and a plurality of light transmitting fibers; wherein themicroendoscope has a cross-sectional area permitting insertion into anasal cavity of a patient.

An illuminating guidewire device is provided, including: a flexibledistal end portion; at least one light emitting element in the distalend portion; at least one structure extending from a proximal end of thedevice through a proximal end portion of the device and at least part ofthe distal end portion to connect the at least one light emittingelement with a power source; a coil; and at least one coil supportwithin the coil, with at least a portion of each coil support fixed tothe coil.

A method of making an illuminating guidewire is provided, including thesteps of: providing a coil having a predetermined length and diameter;inserting mandrels through an annulus of the coil; inserting a firstcore support into the coil and fixing a portion of the first coresupport at a predetermined length from a distal end of the coil;removing a mandrel and inserting a second core support; fixing saidsecond core support at predetermined locations along a length thereof,to the coil and fixing the first core support at additional locationsalong the length thereof to the coil; and inserting illumination fibers.

A transnasally insertable guide system for positioning an endoscope at adesired location within the ear, nose, throat or cranium of a human oranimal subject is provided, including: a tubular guide having anelongate shaft and a lumen, at least a portion of the elongate shafthaving a predetermined shape; a sheath sized to be inserted into thelumen of the tubular guide, the sheath comprising an elongate flexiblebody having a distal end and a scope lumen; and an endoscope that isadvanceable through the scope lumen of the sheath, wherein the endoscopeis useable to view the anatomy when advanced through the scope lumen ofthe sheath having been inserted into the guide and the guide having beeninserted into an internal space within the patient; and wherein thesheath and endoscope are thereafter removable leaving the tubular guidein place.

A guide device useable to position a working device at a desiredlocation within the ear, nose, throat or cranium of a human or animalsubject is provided, including: a transnasally insertable elongate shafthaving a proximal end and a distal end; a channel through which theworking device may be advanced, wherein the shaft comprises an obliquedistal tip.

These and other features of the invention will become apparent to thosepersons skilled in the art upon reading the details of the devices,methods and systems as more fully described below.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1 is a perspective view of one embodiment of a guide system of thepresent invention.

FIG. 2 is a perspective view of the guide system of the presentinvention in use on a human subject.

FIG. 3A is a side view of the guide catheter of the system of FIG. 1.

FIG. 3B is a cross sectional view through line 3B-3B of FIG. 3A.

FIG. 3C is a cross sectional view through line 3C-3C of FIG. 3A.

FIG. 3D is a side view of the endoscope of the system of FIG. 1.

FIG. 3E is a cross sectional view through line 3D-3D of FIG. 3C.

FIG. 3F is a cross-sectional view of a low profile endoscope.

FIG. 3G is a cross-sectional view of another embodiment of a low profileendoscope.

FIG. 3H illustrates a steering mechanism provided in an endoscope thatcan be operated from a proximal end portion of the endoscope.

FIG. 3I illustrates a guide device according to one embodiment of thepresent invention.

FIG. 3J illustrates a distal portion of a guide device having aremovably attached endoscope channel.

FIG. 3K illustrates a snap fitting that may be used to releasably attachan endoscope channel to a main tube of a sinus guide.

FIG. 3L is a side view of the connector/camera/light cable assembly ofthe system of FIG. 1.

FIG. 3M illustrates a snap fitting that may be used to releasablyconnect an endoscope and a sinus guide in a coaxial orientation.

FIG. 4A shows a distal portion of a guide device configured with astatic channel, for accessing a sphenoid sinus.

FIG. 4B shows a distal portion of a guide device configured with astatic channel, for accessing a frontal sinus.

FIG. 5A illustrates a partial plan view of guide device showing oneembodiment of a handle.

FIG. 5B illustrates a longitudinal sectional view of FIG. 5A.

FIG. 6A illustrates another embodiment of a guide device.

FIG. 6B illustrates another embodiment of a guide device.

FIGS. 7A-7C illustrate distal end portions of guide devices havingcurved sections, each with a different radius of curvature.

FIGS. 8A-8D are cross-sectional illustrations showing various placementlocations of an endoscope channel within a main tube of a guide device.

FIG. 9A illustrates a guide device having a distal end with a circulartip.

FIG. 9B illustrates a guide device having a distal end with an obliquetip.

FIG. 9C illustrates an end view of the device of FIG. 9A.

FIG. 9D illustrates an end view of the device of FIG. 9B.

FIG. 10A illustrates the reduced profile of a device having an obliquetip relative to the profile of the device having a circular end that issubstantially perpendicular to the tubing at the end in FIG. 10B.

FIG. 10B shows a device in which both tubes have circular ends that aresubstantially perpendicular to the walls of the tubing.

FIGS. 10C-10D show reduced profiles of oblique tip devices including aset back endoscope channel.

FIG. 11 is a partial perspective view of a guide device of the presentinvention with an optional linking apparatus for linking the endoscopeto a working device to deter divergence of the endoscope away from thepath of the working device.

FIG. 12 is a side view of a guidewire having an angled distal tip.

FIG. 13A shows a step in a method for using a guide system of thepresent invention in conjunction with the guidewire of FIG. 10.

FIG. 13B shows another step in a method for using a guide system of thepresent invention in conjunction with the guidewire of FIG. 10.

FIG. 14 illustrates an example of a procedure in which a guide devicehas been introduced through a nostril and an endoscope has beendelivered through a sinus ostium.

FIG. 15 illustrates a working device having been inserted through theguide device of FIG. 14 and into a sinus cavity.

FIG. 16 illustrates a method in which an endoscope has been insertedthrough a lumen of a working device to enter a sinus cavity.

FIGS. 17A-17D are illustrations of partial sagittal sectional viewsthrough a human head showing various steps of one embodiment of a methodof gaining access to a paranasal sinus using a sinus guide.

FIG. 18 illustrates use of an endoscope inserted through the guidedevice for visualization.

FIG. 19 shows an illuminating guidewire according to one embodiment ofthe present invention.

FIG. 20 illustrates an end view of a semi-cylindrical illuminationfiber.

FIG. 21A shows a core support that may be used to support anilluminating guidewire.

FIG. 21B shows a core support that may be used to support anilluminating guidewire.

FIGS. 21C-21D illustrate a variation of the core support shown in FIG.21A.

FIG. 22A shows an example of a core support formed from an oval wire.

FIG. 22B illustrates a proximal end view of the core support of FIG.22A.

FIG. 23A shows a distal portion of a coil having been stretched to breaktension between adjacent coils and to form an open-pitch portion.

FIG. 23B illustrates insertion of mandrels and a first core support intoa coil.

FIG. 23C shows a cross-sectional view taken along line 23C-23C of FIG.23B.

FIGS. 24A-24B illustrate the sliding ability of core supports relativeto one another during bending of the coil.

FIG. 25A illustrates an embodiment of an illuminating guidewire inproduction showing solder joints employed in this embodiment.

FIG. 25B is a longitudinal sectional view of the guidewire of FIG. 25Ataken along line 25B-25B.

FIG. 25C is an enlarged view of the portion of FIG. 25A surrounded byline 25C.

FIG. 25D is an enlarged view of the portion of FIG. 25B surrounded byline 25D.

FIG. 26 illustrates a step of melting a polymer tube into theopen-pitched portion of the coil.

FIGS. 27A-27B illustrate steps for mounting a connector to a proximalend of the illuminating guidewire.

FIG. 28 illustrates insertion of illumination fibers and formation of adistal lens.

FIG. 29 illustrates finishing steps at a proximal end of theilluminating guidewire.

FIG. 30 shows an embodiment of an illuminating guidewire without aproximal connector.

FIG. 31 illustrates an example of a permanently attached rotating maleluer connector that is attached to a proximal end portion of anilluminating guidewire.

FIG. 32 shows the illumination guidewire of FIG. 30 with a proximalconnector permanently connected thereto.

FIGS. 33A-33B illustrate formation of a preset bend in a core support.

FIG. 34 illustrates a resulting bend in an illumination guidewireemploying a core support having a preset bend.

FIG. 35 illustrates etching the coil.

FIG. 36 illustrates connection of a light cable to an illuminatingguidewire according to one embodiment.

FIG. 37 illustrates a light cable having another connector embodiment.

FIG. 38 illustrates a light cable having another connector embodiment.

FIG. 39 illustrates connection of a light cable to an illuminatingguidewire according to another embodiment.

FIG. 40 shows an illuminating guidewire according to another embodimentof the present invention.

FIG. 41 illustrates an alternative transparent portion that may beincluded in a device shown in FIG. 40.

FIG. 42 illustrates another alternative transparent portion that may beincluded in a device shown in FIG. 40.

FIGS. 43A-43C are illustrations of partial coronal sectional viewsthrough a human head showing various steps of a method for inserting anilluminating guidewire into an ostium that opens to a frontal sinus.

FIG. 44 illustrates a situation where a scope has been inserted as faras possible without causing significant trauma to the patient.

FIGS. 45-47 show additional embodiments of transnasally insertable guidesystems useable to position an endoscope.

DETAILED DESCRIPTION OF THE INVENTION

Before the present devices and methods are described, it is to beunderstood that this invention is not limited to particular embodimentsdescribed, as such may, of course, vary. It is also to be understoodthat the terminology used herein is for the purpose of describingparticular embodiments only, and is not intended to be limiting, sincethe scope of the present invention will be limited only by the appendedclaims.

Where a range of values is provided, it is understood that eachintervening value, to the tenth of the unit of the lower limit unlessthe context clearly dictates otherwise, between the upper and lowerlimits of that range is also specifically disclosed. Each smaller rangebetween any stated value or intervening value in a stated range and anyother stated or intervening value in that stated range is encompassedwithin the invention. The upper and lower limits of these smaller rangesmay independently be included or excluded in the range, and each rangewhere either, neither or both limits are included in the smaller rangesis also encompassed within the invention, subject to any specificallyexcluded limit in the stated range. Where the stated range includes oneor both of the limits, ranges excluding either or both of those includedlimits are also included in the invention.

Unless defined otherwise, all technical and scientific terms used hereinhave the same meaning as commonly understood by one of ordinary skill inthe art to which this invention belongs. Although any methods andmaterials similar or equivalent to those described herein can be used inthe practice or testing of the present invention, the preferred methodsand materials are now described. All publications mentioned herein areincorporated herein by reference to disclose and describe the methodsand/or materials in connection with which the publications are cited.

It must be noted that as used herein and in the appended claims, thesingular forms “a”, “an”, and “the” include plural referents unless thecontext clearly dictates otherwise. Thus, for example, reference to “achannel” includes a plurality of such channels and reference to “theendoscope” includes reference to one or more endoscopes and equivalentsthereof known to those skilled in the art, and so forth.

The publications discussed herein are provided solely for theirdisclosure prior to the filing date of the present application. Nothingherein is to be construed as an admission that the present invention isnot entitled to antedate such publication by virtue of prior invention.Further, the dates of publication provided may be different from theactual publication dates which may need to be independently confirmed.

Sinus Guide with Continuous Endoscope Channel

FIG. 1 shows one embodiment of a sinus guide system 10 of the presentinvention. This sinus guide system 10 comprises a sinus guide 12 and acamera/transmission/endoscope assembly 14. This embodiment of the sinusguide 12 is shown in more detail in FIGS. 3A-3C. As shown, this sinusguide 12 comprises a sinus guide body 26 and an endoscope channel 28 ingenerally side-by-side arrangement. The sinus guide body 26 comprises atube 44 having a lumen 45 (e.g., see FIG. 3B), such as a polymer tubemade of biocompatible polymeric material. A distal end portion 44 d,e.g. a length of about 2 mm may be made of stainless steel, for example,to increase durability, as illustrated in FIG. 3I. Similarly, a distalend portion 28 d of channel 28 can be formed of stainless steel.Alternatively, channel 28 and/or tube 44 can be formed of stainlesssteel along the entire length thereof. Further alternatively, tube 44and/or channel 28 may be formed over an entire length thereof ofstainless steel or other biocompatible metal, except for a polymerdistal tip. Optionally, a liner 46 (FIG. 3B) may be disposed within thelumen 45 of the tube 44. Such liner may be formed of lubricious orsmooth material such as polytetrafluoroethylene (PTFE). Also,optionally, a proximal portion of the tube 44 may be surrounded by anouter tube member 42 formed of material such as stainless steelhypotube. In the embodiment shown, a distal portion of tube 44 extendsout of and beyond the distal end of outer tube 42. This protrudingdistal portion of tube 44 may be straight or curved. Also, it may bepre-formed at the time of manufacture or malleable to a desired shape atthe time of use. When intended for use in accessing the ostium of aparanasal sinus, the distal portion of tube 44 may be curved to form anangle A from about 0 degrees to about 120 degrees. For example, a seriesof sinus guides 12 having angles A of 0, 30, 70, 90 and 110 degrees maybe provided thereby allowing the physician to select the sinus guideangle A that is most appropriate for the particular paranasal sinusostium to be accessed. Additionally, in some embodiments, a rotationgrip 60 may be positioned about a proximal portion of the sinus guide10, as seen in FIGS. 1, 3A and 3B. This rotation grip 60 may have asmooth or textured round outer surface (e.g., it may be a cylindricaltube), or it may have a contoured shape, raised at a distal end portionthereof (as well as, optionally, raised at a proximal end thereof),e.g., see FIG. 3I, to prevent slipping of an operator's hand duringpushing (or pulling) on the handle 60. In any case, handle 60 may begrasped between the fingers of the operator's hand and easily rotated,thereby facilitating rotation (e.g., rolling) of the sinus guide 12 asit is being used. Such rotation of the sinus guide 12 may be desirablefor a number of reasons including but not limited to positioning of thedistal end of the sinus guide 12 at a desired location and/ormaneuvering the location of an endoscope 30 that is inserted through theendoscope channel 28.

The endoscope channel 28 may comprise any structure (e.g., tube, track,groove, rail, etc.) capable of guiding the advancement of a flexibleendoscope. In the particular examples shown in these figures, theendoscope channel 28 comprises a tube (e.g., a polymer tube or stainlesssteel tube or combination of polymer and metal, as noted above) having alumen 29 extending therethrough. In the embodiment seen in FIGS. 1-3C,the endoscope channel 28 is attached to and extends along substantiallythe entire length of the sinus guide body 26. In another embodiment, theendoscope channel 28 can be inside the sinus guide body 26. In otherembodiments, such as described with regard to FIGS. 4A-4C in applicationSer. No. 11/647,530, the endoscope channel 28 may be interrupted,non-continuous or may extend over less than the entire length of thesinus guide body 26. In the embodiment of FIG. 3I, the channel 28extends along the majority of the length of guide body tube 44 and has adistal end portion that conforms to and hugs the curvature of the curveddistal end portion of tube 44. However, the distal end of channel 28ends proximally of the distal end of tube 44. This setback providesmultiple advantages that are described in more detail below. Optionally,the distal end portion of channel 28 can be angled or biased relative tothe direction or orientation of the distal end portion of tube 44. Thisangling or biasing can thus allow the image provided by an endoscopemounted in or on the channel 28 to be aimed toward a particular part ofthe surgical field. For example, the distal end portion of channel 28may be angled or biased slightly inwards (i.e., pointing slightlytowards the distal end of tube 44) so that devices present on the sideof the guide opposite the location of channel 28 can be more easilyvisualized. An outer skin 40 may be heat shrunk or otherwise disposedaround the sinus guide body 26 and endoscope channel 28 to hold theendoscope channel 28 at a desired position on the outer surface of thesinus guide body 26. In FIG. 3I, heat shrink tube or overlamination 40surrounds the tubes 44,28 over a majority of the length of the straightportions of the tubes. Optionally, all or a portion of the curved distalend portions of tubes 44,28 may be surrounded by heat shrink tubing oroverlamination 40 d. Proximal end portions of tubes 44,28 are routedthrough separate channels in handle 60 that angles the tubes apart asthey travel proximally through handle 60, so that luer fittings 45, atthe proximal ends of tubes 40, 28 are spread apart further to make iteasier to insert tools into the tubes 28, 40 and connect to the luers 45with less interference from the other channel 28,40/luer 45.Additionally, the luer 45 for tube 28 can be connected to an irrigationsource (saline-filled syringe or other irrigation source) to inputirrigation fluid through the lumen of tube 28 to deliver fluid acrossthe viewing tip of endoscope 30 having been inserted in the tube 28, inorder to clean the viewing lens. Luer 45 can then be connected to avacuum source to withdraw the fluid from the lens. Alternatively,irrigation or vacuum may be applied separately, to rinse debris off ofthe lens or the suction debris off of the lens, respectively. Furtheralternatively, a suction/irrigation catheter may be inserted throughtube 44 to perform these same functions. This may be advantageous whenthe distal tip of the endoscope 30 has been extended distally of the endof tube 28 and optionally, distally of tube 44.

Alternatively, the endoscope channel 28 may be attached to the sinusguide body 26 at one or more locations by any other suitable attachmentsubstance, apparatus or technique, including but not limited toadhesive, soldering, welding, heat fusion, coextrusion, banding,clipping, etc. The particular circumferential location of the endoscopechannel 28 can be important in some applications, particularly when thesinus guide body 26 includes a curve formed in its distal portion 44. Inthis regard, for some applications, the endoscope channel 28 may beaffixed at a particular circumferential location on the sinus guide body26 to allow a flexible fiber endoscope 30 inserted through the endoscopechannel 28 to provide a view from a desired or optimal vantage point,without obstruction from adjacent anatomical structures. This isdescribed in more detail in application Ser. No. 11/647,530.Alternatively, channel 28 may be located interiorly of the lumen of tube44, and may be positioned at various locations circumferentially aboutthe inner wall of the tube 44. FIGS. 8A-8D show channel 28 mounted tothe inner wall of tube 44 at 6 o'clock, 3 o'clock, 12 o'clock and 9o'clock positions, respectively with regard to tube 44. It is noted thatplacement is not limited to the four relative locations shown, as thechannel may be positioned intermediate of any two of the adjacentlocations shown.

The curve in the distal end portion of channel 28 d, when fixed/staticwith regard to tube 44, must accommodate the rigidity of a distal tipportion of an endoscope as it is passed therethrough, as the endoscope30, although flexible over the majority of its length, is rigid over asmall length extending from the distal tip that contains a lens. In oneexample, an endoscope channel 28 having an inside lumen diameter ofabout 0.045″ can accommodate a rigid distal tip length of about 0.125″on a flexible endoscope 30 having an outside diameter of about 0.0375″with the curved portion of the channel 28 having a radius of curvatureas low as about 0.28″. In one particular example, the radius ofcurvature is about 0.40″. For an endoscope having a rigid distal tiplength of about 0.150″, channel 28 having an inside lumen diameter ofabout 0.045″ can have a curved portion having a radius of curvature aslow as about 0.40″ when the outside diameter of the endoscope is about0.0375″. In one particular example, the radius of curvature is about0.58″ for the rigid distal tip length of about 0.150″.

A camera/cable/endoscope assembly 14 is attachable to arm 43 a or thelower luer fitting 45 shown in FIG. 3I. In the particular embodimentshown in FIGS. 1 and 3L, the camera/cable/endoscope assembly 14comprises an adjustable scope/lock extension 16, an endoscope 18 havingan elongate flexible scope body 30 and integrated light cable 50, acamera 20 and a monitor cable 24. The scope body 30 is advanced throughthe scope/lock extension 16 and through the lumen 29 of the endoscopechannel 28. As shown in FIG. 2, the light cable 50 and monitor cable 24may be connected to console 34 that houses a monitor 36, light source 38and video recorder 40.

FIGS. 3D and 3E show a flexible endoscope 30 attached to a proximal bodymember 52 that engages and attaches to the adjustable scope/lockextension 16. As seen in the cross section of FIG. 3E, the scope 30comprises a flexible shaft having an image fiber bundle 54 that extendscoaxially through the center with light transmitting fibers 56 disposedabout the periphery. In one embodiment, the flexible shaft is a braidedpolyimide sheathing that has a maximum outer diameter of 0.0375 inchesand a length of two feet. The image fiber bundle may be made up of about10,000 thin image fibers and the light transmitting fibers may beillumination fibers with a diameter of between about 0.008 and 0.020inches, with a minimum lux of about 10,000. Of course, fewer or morethan 10,000 fibers may be used to make up the image fiber bundle.Preferably, the distal end of the flexible shaft has a lens with aminimum field of view of about seventy degrees. FIG. 3F is across-sectional illustration of a flexible endoscope 30 having a lowprofile configuration. In this arrangement, the flexible shaft has animage fiber bundle 54 that extends coaxially through the center of theshaft with light transmitting fibers 56 disposed laterally of the imagefiber bundle. Although light transmitting fibers are shown disposedlaterally on both sides of image fiber bundle 54, light transmittingfibers 56 may alternatively be located all on one side of optical fiberbundle 54, as illustrated n FIG. 3G. With either of these arrangements,the height profile of the endoscope shaft 30 is reduced which allowschannel 28 to, in turn be lower profile, thereby reducing thecross-sectional size of the device 12 allowing for it to be more easilyadvanced through the patient anatomy. For example, the cross-sectionalshape of such a low profile endoscope 30 may be substantially oval, asshown in FIGS. 3F-3G, or elliptical Additionally this lowered profilemakes the shaft of endoscope 30 easier to bend/more flexible whenbending in the direction of the arrows shown, and this may allow for asmaller radius of curvature in the curved portion of channel 28 whenchannel 28 is provided with a curve in a distal portion thereof. Itshould be further noted that the light transmitting fibers may bephysically separated from the image fibers in further alternativearrangements. For example, image fibers may extend through an imagefiber light bundle 54, like illustrated in any of FIGS. 3E-3G, whilelight transmitting fibers 56 may run along a different part of the guideor instrument. This separation may allow for some advantages withrespect to fiber flexibility and space constraints. For example, theimage fibers can be positioned together at a proximal end portion of theendoscope, but separate along different arms of a Y-shaped path so thatthe image fibers are inserted through one lumen on the side of the guideor in a main lumen of the guide, while the light fibers are insertedthrough a separate lumen on the side of the guide or in the main lumenof the endoscope, but along a different part of the wall of theendoscope than the part of the wall along which the image fibers run.Thus, rather than providing an endoscope having a single lumen with bothlight fibers and image fibers banded together in the single lumen of theendoscope shaft, the image fibers and the light (illumination) fiberscan be decoupled and inserted separately, at least at the distal endportions, with the proximal end portions being connected to atraditional light source and camera coupler. Alternatively, the imagefibers and illumination fibers can be run separately along the entirelengths thereof, with an image fiber bundle connect to a camera at theproximal end thereof and a separate image fiber bundle can be connectedat the proximal end thereof to a light source. The separate light fiberand illumination fiber bundles can be run through different sides,lumens or parts of the guide.

FIG. 3H illustrates a steering mechanism provided in endoscope 30 thatcan be operated from a proximal end portion of endoscope 30, outside thepatient's body, to steer a distal tip 30 d or portion thereof (e.g.,lens barrel 30 e) to allow directional control of the visual fieldprovided by endoscope 30. As shown, steering mechanism 30 s includes awire extending through endoscope shaft 30 and attached to a side of lensbarrel 30 e, so that when tension is applied via a user pulling on aproximal end portion of wire 30 s, lens barrel 30 e is deflected orangularly directed in the direction shown by the arrow in FIG. 3H. Uponrelease of tension on wire 30 s, lens barrel 30 e resiliently returns toits unbiased orientation and direction. The unbiased orientation anddirection of lens barrel 30 e may be axially aligned with thelongitudinal axis of the endoscope 30 shaft. Alternatively, lens barrelmay be oriented to point angularly away (downward, in FIG. 3H) from thedirection that it is biased toward when tension is applied via steeringmechanism 30 e. In this way, an intermediate amount of tension may beapplied to align the lens barrel 30 e with the longitudinal axis ofendoscope 30 shaft, and a greater amount of tension can be applied tosteer the lens barrel 30 e still further in that direction (e.g.,pointing angularly upwardly in FIG. 3H). Further alternatively, morethan one wire or other steering actuators 30 s may be attached to lensbarrel 30 e for directionally pointing the lens barrel 30 e. Indifferent directions. As one non-limiting example, a second wire 30 scan be mounted on an opposite side of lens barrel 30 e to the side inwhich the first wire 30 s is shown mounted in FIG. 3H. As anotherexample, four wires 30 s can be mounted at ninety degree intervalsaround the circumference of barrel 30 e. Further arrangements forcontrolling along different directions may also be provided, as would beapparent to one of ordinary skill in the art, after reading the abovedescription.

FIG. 3J is a partial view of a sinus guide 12 in which channel 28 isdetachable from tube 44. For example, channel 28 may be attachable toand detachable from tube 44 via snap fit, such as by assembling one ormore snap fittings 51 on tube 44. Snap fitting 51 includes an enclosedlumen 441 through which tube 44 is received, and which forms a frictionfit with tube 44, and a lumen 281 with an opening that allows channel 28to be inserted therethrough. The width of the opening 28 o is less thanthe outside diameter of channel 28, so that when channel 28 is pushedtherethrough, the legs on opposite sides of the opening 28 o aredeformed outwardly to allow tube to pass therethrough. When channel 28has seated in lumen 281, the legs resiliently snap back into theconfiguration shown in FIG. 3K, thereby retaining tube in lumen 281 by asnap fit. Alternatively, lumen 281 can be enclosed and lumen 441provided with an opening, in which case snap fitting 51 would be slidlongitudinally over channel 28 to form a friction fit therewith and tube44 would be inserted through an opening to perform the snap fit. Furtheralternatively, both lumens 281 and 441 can be provided with openings toallow snap fitting of both components in the respective lumens. Stillfurther alternatively, channel 28 may be provided as attachable anddetachable to and from tube 44 via hook and loop type fasteners,adhesives that remain sticky and are thus reusable, or other quickrelease mechanical fasteners. FIG. 3M illustrates a snap fitting 51 thatincludes a lumen 441 in which tube 44 is received forms a friction fitwith tube 44, and a lumen 301 in which endoscope 30 is received to forma friction fit with endoscope 30. Both lumens 441 and 301 includeopenings 40 o and 30 o, respectively. The openings 441 and 301 allow thetube 44 and endoscope 30 to be passed therethrough, respectively. Thewidths of the openings 44 o and 30 o are less than the outside diametersof tube 44 and endoscope 30, respectively. Thus, when tube 44 is pushedthrough opening 44 o, the legs on opposite sides of the opening 44 o areelastically deformed outwardly to allow tube 44 to pass therethrough.Likewise, when endoscope 30 is pushed through opening 30 o, the legs onopposite sides of the opening 30 o are elastically deformed outwardly toallow endoscope 30 to pass therethrough.

The provision of attachable/detachable tube 28 makes it easier to matchthe curve of the distal end portion of channel 28 to the rigiditycharacteristics of the endoscope 30 to be inserted therethrough,particularly the length of the rigid distal tip portion. Thus, forexample, a kit of tubes 28 having distal end portions of varyingcurvatures (and, optionally, having varying lumen diameters) may beprovided so that an appropriate channel 28 can be selected by a surgeonto accommodate the rigidity characteristics of the particular endoscopeto be inserted therethrough, and then the selected tube can be attachedto tube 44.

Alternatively, channel 28 may be inserted independently of tube 44,which may make it easier to locate the distal end portion of channel 28in a target cavity. However, when used separately, this requires use ofa second hand, one to manipulate tube 44 and a second to manipulatechannel 28.

As noted above, the distal end of channel 28 can end proximally of thelocation of the distal end of tube 44, so that the distal end of channel28 is located proximally of the distal end of tube 44 by a setbackdistance 53. Setback distance 53 may be about one mm to about four mm,typically about two mm, for sinus guides having statically placed tubes28. As noted above, placement of channel 28 on a relative location aboutthe circumference of tube 44 may vary, for example for various uses inthe frontal, maxillary and/or sphenoid sinuses. Setback 53 allows thedistal end of endoscope 30 to be advanced distally beyond the distal endof channel 28 without extending distally beyond the distal end of guidebody tube 44, thereby adding protection to the distal end of theendoscope 30 while allowing better visualization when the tip isdistally extended from the distal end of channel 28. This can beparticularly advantageous during advancement of the device 12, forexample.

Additionally, setback 53 also reduces the distal profile of the guidedevice 12, facilitating entry and passage through smaller openings thanallowable by a device that has a distal tip cross sectional area formedby the combined cross sectional areas of tube 44 and channel 28. Setback53 also provides a tapering effect, reducing the physical impact fromendoscope channel 28 as it is traversed through the patient's anatomy.

A distal end portion of channel 28 (including at least distal tipportion 28 d, but which may extend proximally thereof) may be coloredwith a color that contrasts with a color of the remainder of thechannel. This provides visible notice to the user, during traversal ofendoscope 30 over or through channel 28, when the viewing (distal) tipof endoscope 30 has reached the portion having the contrasting color, asthe contrasting color can be visualized on the inner wall surface of thechannel (e.g., lumen), so that the user is aware that the tip of theendoscope is about to be delivered distally of the distal end of channel28. This is possible even when channel 28 is a stainless steel tube. Asthe scope 30 travels through the steel tube 28, even abrasions in thesteel on the inner surface (lumen) are visible. When the endoscopetransitions from the steel tube 28 to the polymer atraumatic tip that iscolored with a contrasting color, a colored ring is visible, which isthe inner wall surface of the colored polymer distal tip 28 d.Additionally, or alternatively, a distal tip portion of tube 44 can becolored with a contrasting color so that this can be visualized as thedistal tip of endoscope is exiting the distal end of channel 28,especially in situations where the distal end of channel 28 isproximally set back from the distal end of tube 44.

The distal tip of channel 28 d is preferably formed as an atraumatictip, having a rounded distal edge. As noted, tip 28 d may be formed ofstainless steel or other hard material. In this case the rounded edgemakes the tip more atraumatic. Alternatively, tip 28 d may be formed ofa softer material such as PEBAX™, SANOPRENE™ (synthetic rubber),silicone, PELLETHANE™ (thermoplastic polyurethane elastomers), or othersoft plastic, which, when formed with a rounded distal edge, evenfurther increases atraumaticity. By providing the atraumatic distaledge, this helps prevent cutting and other damage to tissues as guidedevice 12 is advanced through the patient's anatomy, which may includepushing through tissue, where the atraumatic tip(s) act more like bluntdissectors than cutting instruments. The distal tip of tube 44 can beformed similarly to any of the embodiments of the atraumatic distal tipof channel 28 described above. FIG. 4A shows a distal portion of device12 configured with a static channel 28, for accessing a sphenoid sinus,for example, having tube 44 and channel 28 provided with atraumatic,rounded tips, and wherein a distal tip portion 28 d of channel 28 iscolored with a color that contrasts with a portion of channel 28immediately proximal of tip 28 d. FIG. 4B shows a distal portion ofdevice 12 configured with a static channel 28, for accessing a frontalsinus, for example, having tube 44 and channel 28 provided withatraumatic, rounded tips, and wherein a distal tip portion 28 d ofchannel 28 is colored with a color that contrasts with a portion ofchannel 28 immediately proximal of tip 28 d.

FIG. 5A illustrates a partial plan view of device 12 showing oneembodiment of handle 60. FIG. 5B illustrates a longitudinal sectionalview of FIG. 5A. Handle 60 accommodates channel 28 and tube 44 to passtherethrough and extend proximally thereof to join with connectors 45.Handle 60 may be molded over tube 44 and channel 28 in the configurationshown, or may be molded separately with channels configured anddimensioned to receive channel 28 and tube 44 therethrough (e.g., moldedin halves and then assembled over the tube 44 and channel 28, usingscrews, clamps, adhesives, press fitting, and/or other connectors).Alternatively, the handle can be molded or machined as one piece and thelumens can then be slid into place and fixed with adhesive and/orthreaded connection, etc. Handle 60 is shaped to fit a user's hand, andto be easily rotated by the user. Accordingly, handle 60 may besubstantially barrel-shaped, cylindrical, or other shape that lendsitself to rotation about its longitudinal axis (e.g., rounded about thelongitudinal axis, or octagonal or other extruded polygonalcross-section).

The outer surface of handle 60 can be smooth for easy sliding within thehand, or can be provided with a roughened surface to enhance the grip,for pushing on the handle 60 and/or torquing it. The distal end portionis formed with an uplift, “bump” or increased cross-sectional area 60 b,relative to the mid portion of the handle, to act as a stop against thehand of the user, thereby preventing the hand from sliding distally offof the handle 60 during use.

Channel 28 is guided away from tube 44 at the proximal end portionsthereof, such as by an angled or curved channel 60 c that directs theproximal end portion of channel 28 away from tube 44 as channel 28passes through the channel 60 c. This provides greater separationbetween the connectors 45, facilitating easier insertion of endoscopeinto channel 28 and tools or devices (e.g., balloon catheter, or any ofthe other devices or tools described herein or in application Ser. Nos.11/647,530; 11/522,497; 11/193,020; 10/829,917; 11/116,118; and/or11/150,847; without interference from the other connector 45. Bend orcurve 60 c also creates force feedback and acts as a frictional brakingsystem as endoscope 30 is advanced through channel 28 at the location ofthe bend or curve in channel 60 c, facilitating greater control of theadvancement of the endoscope 30 by the user, with less risk of insertingtoo quickly or impulsively, or overshooting the amount of insertion.Additionally, this helps maintain the endoscope in longitudinal positionrelative to channel 28 even when an additional locking mechanism orvalve is not provided.

Both tube 44 and channel 28 may be provided with a luer connector 45 onproximal ends thereof, to allow for attachment of a syringe forflushing, or attachment of other tools. A Touhy valve or other valve canbe alternatively fitted on the proximal end of channel 28 to facilitatelocking of the endoscope 30 in a position relative to channel 28.Further alternatively, a Y-adapter may be fitted to the proximal end ofchannel 28 to permit fixation of luer 45 to one arm of the Y and a valveto the other arm. Numerous other accessories can be attached to eitherchannel 28 or tube 44, including drip systems, pop-off valves, etc.

FIG. 6A illustrates an embodiment of sinus guide device 12 whereinendoscope channel 28 is fixed relative to handle 60 and tube 44 isrotatable about its longitudinal axis within handle 60. Accordingly, thelocation of channel 28 relative to tube 44 can be varied by rotatinghandle 60 and holding the luer connector 45 that connects to tube 44stationary as the handle 60 is rotated. This causes channel 28 torevolve about the longitudinal axis of tube 44, thereby repositioningthe radial position of channel 28 relative to tube 44. For example, withchannel 28 in a radial position at the top of tube 44 as illustrated inFIG. 6A, luer 45 connected to tube 44 can be grasped and prevented fromrotating while rotating handle 60. By rotating handle 60 by 180 degrees,this results in channel 28 being positioned at the bottom side of tube44. This rotatability to reposition channel 28 provides re-orientationof the view provided through endoscope 30 that is positioned through orover channel 28. The channel in handle 60 receiving tube 44 providessome frictional resistance to rotation of tube 44 relative thereto, sothat tube 44 will not rotate relative to handle 60 during use of device12, except when the user deliberately holds the connector 45 or tube 44to prevent it from rotating and then rotates handle 60. Additionally, oralternatively, the channel in handle 60 receiving tube 44 and tube 44may be provided with at cooperating detents and recesses which engage atpredetermined rotational positions of the tube 44 relative to thechannel. Thus, as the user rotates the handle 60 around tube 44, thereare predetermined configurations where the detents engage the recessesto provide friction resistance to rotation. These detents and recessescan be placed in strategically important locations with respect to theangle of the distal end portion of tube 44. For example, it may beadvantageous to have on such predetermined position/orientation with theendoscope channel 28 lined up with the greater curvature of the distalend portion 44, “riding the back of the guide”, as illustrated in FIG.6A. Another predetermined position/orientation may be 180 degreesrotated relative to the previously described position. Of course, theplacement of detents and recesses can be configured to provideadditional, or alternative orientations, as desired. FIG. 6A also showschannel 28 having a distal tip positioned proximally of the curvedsection of tube 44. This may be advantageous for example, for use in themaxillary sinus, to provide a larger, or wider angle view of themaxillary sinus by setting the distal tip of channel 28 proximally awayfrom the curve. It is noted that the rotatability functions and featuresdescribed with regard to FIG. 6A are not limited to this embodiment witha shortened channel 28. For example, this rotatability can also beprovided with a device 12 like that shown in FIG. 4A.

FIG. 6B illustrates a variation of a rotatable device 12. In thisarrangement, a second handle 61 is provided proximally of handle 60.Handle 61 is fixed relative to tube 44, so that the user can hold handle61 to prevent it and the tube 44 from rotating as the user rotateshandle 60 to revolve channel 28 about tube 44. Optionally, handle 61 maybe spring-biased into contact with handle 60 to act as a brake toprevent handle 60 from rotating relative to handle 61. In order toperform a rotation in this case, the user pulls handle 61 proximally outof contact with handle 60 to relieve the braking force and allow theuser to rotate handle 60 while holding handle 61 stationary. Furtheroptionally, the frictional force imposed by handle 61 against handle 60may be great enough to prevent relative rotation during use of device12, but can be overcome by the user twisting on handle 60 and holdinghandle 61 stationary, without the need to retract or reposition handle61 relative to handle 60. As with the embodiment of FIG. 6A, theembodiments of the rotational features described with regard to FIG. 6Bcan be employed in other guide device 12 embodiments, and are notlimited to a device having a channel 12 that ends proximally of a bendin tube 44.

For devices 12 in which distal end portions of tube 44 and channel 28are curved, and channel 28 comprises a tube, the radius of curvature canbe designed to readily allow the endoscope 30 (and particularly thedistal tip portion that includes the lens, which may be rigid) to movethrough the lumen of tube 28 and around the curve without the need toincrease the inside diameter of the lumen, so that the lumen can bedesigned with an inside diameter having only a small tolerance aroundthe outside diameter of endoscope 30. Typically, standard 18 gaugehypotube is used having an outside diameter of about 0.050″. The wallthickness is selected is as thin as possible, to maximize the insidediameter of the tube without risking buckling of the tube. Typically thewall thickness is about 0.003″. In one particular example, the tube is18 Gauge UTS with an outside diameter of 0.050″+0.001″/−0.0005″, with aninside diameter of about 0.044″ and therefore a tolerance of about+0.0015/−0.001″. Alternatively, the inside diameter of tube 28 can beincreased if the curvature of the distal end portion is required to havea radius of curvature that would not allow the endoscope to passotherwise. The amount of curvature that can be successfully used with alumen of normal tolerance relative to the outside diameter of endoscope30 will also vary with the degree of flexibility of the endoscope 30 andthe length of the lens barrel 30 e. In other words, the longer that thestiff section (lens barrel and adhesive) is, the bigger is the requiredinside diameter of tube 28 and/or the bigger the required radius ofcurvature of a bend in a tube 28 to allow easy passage of the stiffsection. FIGS. 7A-7C illustrate exemplary distal end portions of devices12 in which the curvatures of tubes 28,40 are varied, wherein the largerthe radius of curvature, the easier it is to pass endoscopetherethrough, with all other variables being constant. In FIG. 7A, theradius of curvature is about 0.25 inches, in FIG. 7B, the radius ofcurvature is about 0.5 inches, and in FIG. 7C, the radius of curvatureis about 0.75 inches. The insider diameters of the tubes 28 in theseexamples are 0.044″+0.0015″/−0.001″.

In order to reduce the distal end profile of the guide device 12, tube44 may be provided with a non-circular cross-section at the distal endthereof. By reducing the distal end profile, this facilitates entry andpassage through smaller openings or relatively more constrained spaces,such as may be encountered in the passages leading to the frontal ormaxillary sinuses, or other spaces relatively constrained by thepatient's anatomy, as the reduced cross-sectional profile of the distalend of tube 44 is more readily able to be introduced into smaller orpartially obstructed spaces, compared to tubes having a full circulardistal end cross-section. FIG. 9A illustrates tube 44 having a standard,circular cross-section at its distal end. FIG. 9B illustrates tube 44having a reduced cross-sectional area at its distal end, in this caseformed by an oblique tip (e.g., a scooped-tip) 44 t. Because a portionof the distal end of tube 44 is cut away to form the scooped tip, theprofile of the distal end of tip 44 t is significantly less than that ofthe tube 44, as it recedes obliquely over a cross-section thereof, asillustrated by comparing FIGS. 9C and 9D, which illustrate the distalend profiles of the tube 44 in FIGS. 9A and 9B, respectively.Accordingly, the cross-sectional profile of the oblique tip 44 t tapersdown from that of a circular profile, at a proximal end of the obliquetip 44 t, to a semi-circle or less at the distal end of the oblique tip44 t. In addition to the advantages noted above, a tube 44 having areduced-profile tip, such as an oblique tip 44 t, for example, mayfacilitate entry into, or closer position to ostia by the distal end ofa guide device 12. The oblique tip 44 t design may also facilitateballoon retraction (of a balloon catheter), back into tube 44 afterperforming an ostial dilatation procedure, for example.

In particular, with regard to the maxillary sinus, the taperedcross-section provided by oblique tip 44 t allows the distal end of tube12 to be easily passed behind the uncinate process. In the frontalrecess, the oblique tip 44 t may provide additional freedom of movementof device 12.

In addition to providing a significantly reduced cross-sectional area atthe distal end, oblique tip 44 t of FIG. 9B also provides a largeropening than the circular opening of the standard tube end, like shownin FIG. 9A, for tubes 44 having the same inside diameter. Accordingly,as mentioned above, this may make it easier to retract a balloon portionof a balloon catheter back into the lumen of tube 44, e.g., afterperforming a dilatation procedure and deflating the balloon.Additionally, the curvature of the sides of the oblique tip (scoopshape), tapering down to the proximal end of the oblique tip (scoopshape) can facilitate folding of the balloon as it is retracted into thelumen of tube 44.

The oblique tip 44 t can be provided on a guide device 12 that does notinclude an endoscope channel, as illustrated above with regard to FIG.9B. Further the advantages discussed above can also be provided to aguide device 12 that does include a channel 28 integrated therewith. Thechannel 28 may be fixed relative to tube 44 and may be removably fixed,as described previously. FIG. 10A illustrates an example of guide device12 having a fixed channel 28 that extends so that the distal end ofchannel 28 is substantially flush with the distal end of oblique tip 44t. Although this arrangement is not preferred as it is preferred toprovide a setback, even with this arrangement, the reducedcross-sectional profile at the end of oblique tip 44 t compensates, orhelps to compensate for the additional cross-section profile of the endof channel 28. That is, the cross sectional dimension 12×1 is less thanthe cross-sectional dimension 12×2 measured across the distal ends oftubes 44 and 28 when tube 44 has a circular profile distal end as shownin FIG. 10B.

An even greater advantage in reducing the distal end profile of a device12 having both tube 44 and channel 28 can be obtained by orienting thedistal end of channel 28 with a setback 53 as described above and asillustrated in FIGS. 10C and 10D. Regardless of whether the bend in thetube 44 and channel 28 is an acute angle or an obtuse angle (or rightangle), the distal end cross-sectional dimension 12×1 is greatly reducedrelative to 12×2 in FIG. 10B, and even the cross-sectional dimension12×3 that includes the profile of channel 28, but is set back from thedistal end of device 12, is reduced relative to 12×2.

Optional Linkage of Endoscope to Working Device

In some applications, it may be desirable to advance the flexibleendoscope 30 out of and beyond the distal end of the endoscope channel28, 28 d, and even beyond the distal end of tube 44. For example, asshown in FIG. 11, the endoscope 30 may sometimes be advanced along sidea working device, such as a guidewire 110, so as to view theadvancement, positioning and/or use of the working device. In suchinstances, it is desirable to prevent the endoscope from diverging awayfrom the working device and/or to maintain the endoscope 30 at aspecific spaced distance away from the working device. To accomplishthis, an optional linkage device 62 may be used to link (e.g., couple,connect or attach) the endoscope 30 to the guidewire 110 or otherworking device. Other working devices that may be inserted through tube44, and optionally linked to endoscope 30 via linkage device 62,include, but are not limited to: graspers, catheters, instrument orother device useable to perform or facilitate a therapeutic ordiagnostic task such as local or regional drug delivery, biopsy,suction, irrigation, polyp removal, fungal ball removal or other massremoval.

Operation and Positioning of the Endoscope and Working Device

As noted, the flexible fiber endoscope 30 may be freely advanced to orbeyond the end of the sinus guide 12 and retracted during use, in orderto facilitate endoscopic viewing of the desired anatomical structuresand/or to view, guide and/or verify the positioning of the sinus guidedevice 12 or a working device that has been inserted through the sinusguide. The ability to advance the tip of the flexible fiber endoscope 30beyond the end of the sinus guide allows the tip to be positioned closerto anatomy or to reach spaces in the paranasal sinuses that the sinusguide tip cannot travel to due to size constraints.

In some instances, it may be desired to advance a guidewire 110 into orthrough a specific body opening, such as an opening of a paranasalsinus. In such applications, as shown in FIG. 12, it is sometimesdesirable to form a bend in the guidewire 110 near its distal end DE sothat rotation of the guidewire in situ will redirect its distal end DE.The guidewire may be maneuvered into the opening by simply rotating theguidewire 110. FIGS. 13A and 13B show an example of such a procedure,wherein the guide device 12 is advanced to a position where its distalend is a spaced distance D from the opening O into which the guidewire110 is to be inserted. In some instances, the user may use fluoroscopyand/or a surgical navigation system to position the guide device asdescribed in previous applications to which this application claimspriority and which have been incorporated herein by reference. With theguide device 12 so positioned, an endoscope inserted through theendoscope channel 28 may be used to view the distal end DE of theguidewire 110 as it advances out of the distal end of the sinus guidebody tube 44. With the flexible endoscope 30 so positioned, the user hasa view generally along the same axis as the distal opening of the guidedevice, rather than the proximal axis of the guide device. Furthermorethe view can be from behind anatomy that normally would block aconventional endoscope view. In FIG. 13A, the view provided by theendoscope allows the operator to see that the distal end of theguidewire 110 is not directed into the opening O. As a result, theoperator may rotate the guidewire 110 causing its distal end DE to bedirected into the opening O as verified by the view provided from theendoscope. Thus, in these sorts of applications, it is desirable toplace the distal end of the sinus guide device 12 at a spaced distance Dback from the opening O rather than advancing it to a point where thedistal end of the sinus guide body is immediately adjacent to or withinthe opening O. In an alternative embodiment, the guidewire can be anilluminating guidewire as described in co-pending application Ser. Nos.11/522,497 and 11/647,530, or as described herein.

Use of Flexible Endoscope with Intra-Sinus Procedures

Many current FESS procedures are performed to open sinus ostia. Also,balloon dilatation of sinus ostia can be performed in a balloonsinuplasty procedure, embodiments of which have been discussedpreviously in co-pending applications incorporated by reference herein.The flexible endoscopes described herein can be utilized, with orwithout guide device 12 to facilitate direct visualization of suchprocedures.

However, until now, the number of procedures performed inside a sinuscavity have been limited, due to challenges with visualizing suchprocedures, since direct visualization was not possible, due to theprohibitive profile sizes and rigidity of endoscopes conventionally usedin the procedures. The current invention provides flexible endoscopes 30as small as about one mm outside diameter and may be semi-rigid. Thissmall outside diameter of endoscope 30 permits it to be inserted throughan ostium either pre- or post-dilation of the ostium to provide directvisualization inside the sinus cavity. This visualization capability maytherefore facilitate direct viewing of intra-sinus therapies, treatmentsand procedures.

FIG. 14 illustrates an example of a procedure in which sinus guidedevice 12 has been introduced through a nostril 2 of a patient 1 andthrough a nasal cavity to a location close to an ostium 1014 of a sinus1016. Endoscope 30 may be used in a position where the distal tip of theendoscope is flush with the opening 28 d of channel 28, extends distallybeyond distal end 28 d, but not distally beyond the distal end of tube44, or slightly distally beyond the distal end of tube 44 to providedirect visualization of a procedure to dilate the ostium 1014, forexample. In some cases, intra-sinus procedures may be commenced withoutdilating the ostium 1014. Accordingly, either without dilatation of theostium 1014, or before of after dilatation of ostium 1014, endoscope 30is further distally advanced through the ostium to position the distalviewing tip of the endoscope within the sinus 1016, as shown in FIG. 14.A variety of therapies may be delivered into the sinus with directvisualization thereof provided by endoscope 30 positioned in the sinus1016, including, but not limited to: local or regional drug delivery,biopsy, suction, irrigation, polyp removal, fungal ball removal and/orremoval of other mass. Endoscope 30, when positioned in a sinus 1016 mayalso be useful for intra-sinus diagnosis to assess an underlyingdisease, to evaluate ciliary function by viewing transport of a dyedfluid, or other diagnostic procedure. These therapeutic and diagnosticprocedures may additionally be facilitated by insertion of one or moretools, instruments or devices through the lumen of tube 44 to deliver aworking end portion of the tool, device or instrument through the ostium1014 and into the sinus 1016. A variety of tools, instruments or devicesmay be inserted through tube 44, including, but not limited to:graspers, cutters, punches, flexible microdebriders, dissectors,electrodes for energy delivery (RF, heat, cryotherapy, ultrasound, ormicrowave), lasers, suction catheters, irrigation catheters, ballooncatheters, etc.

FIG. 15 illustrates an intra-sinus procedural step in which endoscope 30has been positioned intra-sinusly, in sinus 1016 in a manner asdescribed above with regard to FIG. 12. Additionally a flexible graspersinstrument 1007 has been inserted through a lumen of tube 44 andadvanced to deliver the distal, working end into the sinus 1016. Byviewing the working end of the graspers 1007 through endoscope 30, anoperator can advance the working end and operate the grasping jaws 1007j to approach a mass 1016 m in the sinus that is desired to be removed,position the jaws 1007 around the mass 1016 m or a portion thereof, andclamp the jaws to capture the mass 1016 m or a portion thereof. By thenretracting tool 1007, the mass 1016 m or a portion thereof that has beencaptured by jaws 1007 j can be withdrawn through ostium 1014, withvisualization of all of these steps being facilitated through endoscope30. The mass 1016 m or a portion thereof having been captured and tornaway or otherwise removed from the sinus 1016 and through ostium 1014 isthen withdrawn through tube 44. Alternatively, viewing of retraction ofthe mass into the tube 44 can be performed by retracting the distal endof endoscope 30 to a location just proximal of ostium 1014 or justproximal of the distal end of tube 44. Further alternatively, if themass 1016 m is too large to be retracted through tube 44, device 12 canbe removed simultaneously with the removal of tool 1007 and the mass1016 m.

It is noted that FIG. 15 is only one example of procedures that can beperformed intra-sinusly and that the present invention is by no meanslimited to this procedure, as many other procedures can be performed,some examples of which were listed above.

FIG. 16 illustrates an alternative procedure in which endoscope 30 isinserted through a lumen of a tool, device or instrument having beeninserted through tube 44 of guide device 12 and into a sinus cavity1016. In the example shown, endoscope 30 has been inserted through thelumen of an irrigation catheter 330. Note also that device 12 mayinclude an integrated endoscope channel 28, but need not, since theendoscope, in this example, is delivered through the same lumen in tube44 that the working tool is delivered through. In the example shown inFIG. 16, device 12 does not include an endoscope channel 28. It isfurther noted that this technique is not limited to insertion ofendoscope 30 through an irrigation catheter, as endoscope 30 may besimilarly inserted through any other tool, instrument or device havingbeen inserted through tube 44 and which has a lumen with a sufficientinside diameter to allow endoscope 30 to pass therethrough. Also,although reference here is made to the tool, instrument or device havinga distal end portion inserted into a sinus cavity 1016, endoscope 30 maybe used similarly to view locations outside of an ostium 1014, when thedistal end of the tool, instrument or device ahs not been insertedthrough the ostium, or to view some other cavity or space, for example.

In the example shown, an irrigation procedure is first performed in thesinus 1016 prior to insertion of endoscope 30 into the lumen of theirrigation catheter 330. In this particular example, irrigation catheterhas a lumen having a diameter of about 0.050″ and endoscope 30 has anoutside diameter of about 0.0375″. Accordingly, after performingirrigation with the distal end of irrigation catheter 330 in the sinus16, endoscope 30 is inserted through the lumen of the irrigationcatheter 330 and advanced to deliver the distal (viewing) tip into thesinus cavity 1016, as shown. The user can then view through endoscope 30to confirm whether the sinus 1016 has been cleaned out sufficiently bythe irrigation process, and/or to inspect the sinus for other potentialissues or ailments that might be addressed.

Illuminating Guidewire

FIGS. 17A through 17D are illustrations of partial sagittal sectionalviews through a human head showing various steps of one embodiment of amethod of gaining access to a paranasal sinus using a sinus guide 12. InFIG. 17A, a first introducing device in the form of a sinus guide 12 isintroduced through a nostril and through a nasal cavity 1012 to alocation close to an ostium 1014 of a sphenoid sinus 1016. Sinus guide12 may be straight, malleable, deflectable or shapeable at the tip, orit may incorporate one or more preformed curves or bends as furtherdescribed above, as well as in U.S. Patent Publication Nos. 2006/004323;2006/0063973; and 2006/0095066, for example, each of which areincorporated herein, in their entireties, by reference thereto. Inembodiments where sinus guide 12 is curved or bent, the deflection angleof the curve or bend may be in the range of up to about 135 degrees.

In FIG. 17B, a second introduction device comprising a guidewire 110 isintroduced through the first introduction device (i.e., sinus guide 12)and advanced so that the distal end portion of guidewire 110 enters thesphenoid sinus 1016 through the ostium 1014.

In FIG. 17C, a working device 1006, for example a balloon catheter 100,is introduced over guidewire 110 and advanced to extend the distal endportion of device 1006, 100 into the sphenoid sinus 1016. Thereafter, inFIG. 17D, working device 1006, 100 is used to perform a diagnostic ortherapeutic procedure. In this particular example, the procedure isdilatation of the sphenoid sinus ostium 1014, as is illustrated in FIG.17D, where the balloon of device 1006 is expanded to enlarge the openingof the ostium 1014. After completion of the procedure, sinus guide 12,guidewire 110 and working device 1006, 100 are withdrawn and removed. Itwill be appreciated that the present invention may also be used todilate or modify any sinus ostium or other man-made or naturallyoccurring anatomical opening or passageway within the nose, paranasalsinuses, nasopharynx or adjacent areas. As will also be appreciated bythose of ordinary skill in the art, in this or any of the proceduresdescribed in this patent application, the operator may additionallyadvance other types of catheters, and that guidewire 110 may besteerable (e.g. torquable, actively deformable) or shapeable ormalleable.

FIGS. 17B-17D show endoscope 30 having been inserted through channel 28to provide visualization of advancement of sinus guide 12 and/orinserted alongside sinus guide 12 to provide visualization of all or atleast a portion of working tool 1006, 100. It is to be appreciated thatscope 30 may comprise any suitable types of rigid or flexible endoscopeand such optional scope may be separate from or incorporated into theworking devices and/or introduction devices of the present invention, asfurther described herein. In one preferred embodiment, endoscope 30 is aflexible fiber endoscope 30 as described herein.

In cases where a scope 30 provided is not capable of being inserted intoa particular sinus cavity of interest, or to extend the view ofendoscope or otherwise assist visualization through the endoscope,and/or to provide visualization for guiding guidewire 110 into the sinuscavity either prior to insertion of endoscope in the cavity or whereendoscope 30 is incapable of being inserted into that particular cavity,an illumination guidewire 110 may be utilized to enhance visualization.

Further, depending upon the particular configuration of the sinuspassageways to be traversed to gain access to a target ostium, the scope30, due to physical limitations (e.g., outside diameter, degree ofrigidity, etc.) may be unable to visualize as deep as the location ofthe ostium of interest. For example, FIG. 18 illustrates a situationwhere scope 30 has been inserted as far as possible without causingsignificant trauma to the patient. The range of adequately illuminatedvisibility in this case does not extend all the way to ostium 1020, asindicated schematically by the rays 1009 shown extending distally fromscope 30. In this case, adequately illuminated visualization ofguidewire 110 into ostium 1020 would not be possible via scope 30.Additionally, if sinus guide 12 is physically capable of being extendedfurther distally to place the distal end thereof at the approach toostium 1020, scope 30 would also not be capable of adequatelyvisualizing this. Thus, prior to the provision of an illuminatedguidewire 110 as described herein, fluoroscopic or other x-rayvisualization of these procedures was required, in order to ensure thatthe devices approach (and extend through) the appropriate ostium 1020and not another adjacent opening, such as opening 1024.

In order to overcome these and other problems, the guidewire devices 110of the present invention include their own light emitting capability. Byilluminating a distal end portion of guidewire 110, a process known astransillumination occurs as guidewire 110 traverses through the sinuspassageways, passes through an ostium and enters a sinus cavity.Transillumination refers to the passing of light through the walls of abody part or organ. Thus, when guidewire 110 is located in a sinus, thelight emitted from guidewire 110 passes through the facial structuresand appears as a glowing region on the skin (e.g., face) of the patient.It is noted that the light emitted from scope 30, such as positioned inFIG. 18, for example, results in transillumination as well, but theresultant glow is much more diffuse and larger in area. As the lightsource in guidewire 110 gets closer to the surface of the structure thatit is inserted into (e.g., the surface of the sinus), thetransillumination effect becomes brighter and more focused (i.e.,smaller in area). Additionally, the movements of the guidewire 110 canbe tracked by following the movements of the transillumination spotproduced on the skin of the patient. For example, the light emissionportion of illumination guidewire can cause transillumination asguidewire 110 is being manipulated to gain access to an ostium andsinus. By tracking movements of a transillumination spot that moves asthe illuminating portion of the guidewire 110 is moved during themanipulation, this can provide feedback to the user about steering andpositioning and whether or not they are successful in entering throughthe ostium and into the sinus of interest. For example,transillumination may be visible on the bridge of the nose when gainingaccess to the frontal sinus. If the user positions the illuminatingguidewire 110 medially, transillumination may show in the medial aspect.As the user looks for the frontal recess, he may then move theilluminating guidewire 110 laterally. Transillumination can then confirmthat the distal end portion of the guidewire has indeed been movedlaterally, as the user tracks the lateral movement of the illuminationspot.

FIG. 19 shows an illuminating guidewire 110 according to one embodimentof the present invention. Device 10 includes a flexible distal endportion 110 d that provides a similar degree of flexibility to astandard, non-illuminating type of guidewire. Distal end portion 110 dmay include a coil 110 c as an exterior portion thereof, to help providethe desired flexibility to this portion. The proximal end portion 110 pof device 110 extends the device to provide a sufficient length so thatdevice 110 extends proximally out of the patient (and, when insertedthrough another device, such as a sinus guide 12, proximally out of thedevice into which guidewire 110 is inserted), at all times, includingthe deepest location into which the distal end of device 110 is placed.The proximal end portion 110 p can have visible markings, preferablyspaced at equal intervals, that can be observed by the user to confirmhow far the guidewire 110 has been placed in the patient. Proximal endportion 110 p also provides the necessary mechanical properties requiredto make the guidewire function properly. These mechanical propertiesinclude torquability, i.e., the ability to torque the proximal endportion 110 p from a location outside of the patient and have thattorque transmitted to the distal end portion 110 p; pushability, i.e.,sufficient rigidity, so that when an operator pushes on the proximal endportion 110 p from a location outside of the patient, the pushing forcetransmits to the distal portion 110 d to advance the distal portion 110d without buckling the device 110; and tensile strength so that anoperator can pull on the proximal end portion 110 p from a locationoutside of the patient and withdraw device 110 from the patient withoutsignificant plastic deformation or any disintegration of the device.

Coil 110 c may be formed from a stainless steel wire, for example. Inthe examples shown, coil 110 c is formed as a single wind coil, i.e.,from a single wire. Alternatively, coil 110 c may be formed by multiplewires coiled simultaneously to form a single coil 110 c from multiplewires. The diameter of the coil wire can be between about 0.004 andabout 0.008 inches, typically about 0.006 inches. In one particularembodiment, coil 110 c is made of stainless steel wire having a diameterof about 0.006 inches, coiled into a coil having an outside diameter ofabout 0.033 inches. Use of wire having a larger diameter provides addedstrength to the coil, but at the same time requires a larger outsidediameter coil, which makes the overall device 110 more difficult toadvance through small openings, but also allows more space in the insidediameter of the coil. Alternative materials from which coil 110 c may beformed include, but are not limited to: ELGILOY®, CONICHROME® or otherbiocompatible cobalt-chromium-nickel alloy; nickel-titanium alloys, orother known biocompatible metal alloys having similar characteristics.Further alternatively, distal end portion may comprise a braidedmetallic construction of any of the aforementioned materials in lieu ofa coil.

The external casing of the proximal portion 110 p can be made from apolyimide sheath, a continuous coil (optionally embedded in polymer orhaving polymer laminated thereon), a hypotube (e.g., stainless steelhypotube), a laser-cut hypotube, a cable tube, or a tube made fromPEBAX® (nylon resin) or other medical grade resin. In any of these casesthe construction needs to meet the required torquability, pushabilityand tensile requirements of the device.

In the example shown, coil 110 c is joined to proximal portion 110 p bysolder, epoxy or other adhesive or mechanical joint. One or moreillumination channels 110 i are provided in device 110 and extend thelength thereof. Illumination channels 110 i are configured to transportlight from the proximal end of device 110 to and out of the distal endof device 110. In the example shown, two illumination channels areprovided, each comprising a plastic illumination fiber. The plastic usedto make the illumination fibers is compounded for light transmissionproperties according to techniques known and available in the art. Asone example, ESKA™ (Mitsubishi Rayon), a high performance plasticoptical fiber may be used, which has a concentric double-layer structurewith high-purity polymethyl methacrylate (PMMA) core and a thin layer ofspecially selected transparent fluorine polymer cladding. In oneexample, illumination fibers each have an outside diameter of about0.010″. In one example, two acrylic light fibers each having an outsidediameter of about 0.10″ are used. The illumination fibers can have anoutside diameter in the range of about 0.005 inches to about 0.010inches. Alternatively, a single plastic illumination fiber 101 may beused that has an outside diameter of about 0.020″. As anotheralternative, a single light fiber having an outside diameter of about0.010″ can be used. This provides additional internal space for othercomponents, but halves the light output compared to embodiments usingtwo 0.010″ fibers. FIG. 20 illustrates another alternative, in which asingle, semi-cylindrical light (illumination) fiber is used, wherein thediameter 109 is about 0.020″. This half-round or semi-cylindrical fiberfrees up additional internal space in the device, relative to use of twocylindrical fibers of 0.010″ each, and provides about the sameillumination output. However, these fibers are expensive and timeconsuming to manufacture. Other illumination fibers 110 havingcustom-shaped cross sections may be alternatively used, but again may beexpensive and difficult to manufacture. Further alternatively, glassillumination fibers may be substituted which are much smaller in outsidediameter, e.g., about 0.002″. In this case, more illumination fibers maybe provided in a bundle, e.g., about six to fifty glass fibers 110 i maybe provided.

The distal end of device 110 is sealed by a transparent (or translucent)seal 110 s which may be in the form of epoxy or other transparent ortranslucent adhesive or sealing material, which may also function as alens. For example, seal 110 s may be formed of a translucent,ultra-violet curing adhesive to form a distal lens of the guidewire 110.Alternatively, other translucent or transparent and biocompatibleadhesives or epoxies may be substituted. Seal 110 s maintains the distalends of illumination fibers 110 i coincident with the distal end ofdevice 110 and also provides an atraumatic tip of the device 110.Further, seal 110 s prevents entrance of foreign materials into thedevice. The distal end can be designed to either focus or distribute thelight as it emanates therefrom, to achieve maximum transilluminationeffects. In this regard, the distal end can include a lens, prism ordiffracting element.

The proximal end of device 110 may also be sealed by a transparent (ortranslucent) seal 110 ps which may be in the form of epoxy or othertransparent or translucent adhesive or sealing material. Seal 110 psmaintains the proximal ends of illumination fibers 110 i coincident withthe proximal end of device 110. The proximal end of device 110 may befurther prepared by grinding and polishing to improve the opticalproperties at the interface of the proximal end of device 110 with alight source. The illumination fibers 110 i at locations intermediate ofthe proximal and distal ends need not be, and typically are not fixed,since no mapping of these fibers is required, as device 110 providesonly illumination, not a visualization function like that provided by anendoscope. Further, by leaving illumination fibers free to move atlocations between the proximal and distal ends, this increases theoverall flexibility and bendability of device 110 relative to a similararrangement, but where the illumination fibers 110 i are internallyfixed.

The outside diameter of device 110 may be in the range of about 0.025inches to about 0.040 inches, typically about 0.030 to 0.038 inches, andin at least one embodiment, is about 0.035″±0.005″. At least theproximal portion 110 p of device 110 is provided with a core support 110cw that is contained therein. In the example shown in FIG. 19, coresupport 110 cw is a wire that is fixed to proximal section 110 p such asby laser welding, epoxy or other adhesive or mechanical fixture. Coresupport 110 cw may extend substantially the full length of device 110.In any case, core support 110 cw is typically formed from stainlesssteel NITINOL (nickel-titanium alloy) or other biocompatiblenickel-titanium alloys, cobalt-chromium alloys, or other metal alloysthat are biocompatible and provide the necessary rigidity andtorquability. Core support 110 cw may be formed as a wire, as in theexample shown in FIG. 19, or alternatively, may be braided from any ofthe same materials or combination of materials mentioned above. Coresupport 110 cw, when formed as a wire can be ground to differentdiameters to provide varying amounts of rigidity and torquability. Whenformed as a braid, the braid can be formed to have varying amounts ofrigidity and torquability along the length thereof. For example, corewire 110 cw has a larger outside diameter at the proximal end portionthan at the distal end portion so that it is more rigid and transfersmore torque from the proximal portion of device 110, whereas at thedistal end portion, core 110 cw is relatively more flexible andtwistable. For core supports 110 cw that extend through proximal portion110 p, the portion of core support near the proximal end of device 110may have an even larger outside diameter. It may be advantageous toshrink the illumination fibers 110 i by heating them above apredetermined temperature (e.g., greater than about 52 degrees C.)before sealing them on both ends.

In at least one embodiment, two core supports 110 cw and 111 cw areprovided in guidewire 110. FIGS. 21A-21B illustrate an embodiment of thefirst 110 cw and second 111 cw core supports, respectively. In FIG. 21A,core support 110 cw may be formed from a nickel titanium alloy core wirehaving a diameter of about 0.008″, although a similar configuration canbe made starting with a core wire of different material and/or differentdiameter. A proximal portion 1130 p of core support 110 cw is maintainedas the full wire profile having the diameter of 0.008″. An intermediatesection 1130 i is ground down to a 0.006″ diameter for greaterflexibility in a distal end portion of the guidewire 110. The distal endportion 1130 d is flattened, which facilitates soldering core support110 cw to coil 110 c. The length of flattened section 1130 d ismaintained small, e.g., about 0.8 cm to prevent guidewire whipping.Alternatively, flattened section 1130 d may be eliminated altogetherwith the reduced diameter round cross section 1130 i extending to thedistal end of core support 110 cw. The length of the section 1130 i(whether or not flattened section 1130 d is employed) may be varied tocustomize the length of a flexible distal end portion of guidewire 110.

In FIG. 21B, core support 111 cw that may be formed from a nickeltitanium alloy core wire having a diameter of about 0.006″, although asimilar configuration can be made starting with a core wire of differentmaterial and/or different diameter. Proximal portion 1130 p of coresupport 111 cw is maintained as the full wire profile having thediameter of 0.006″. A distal end portion 1130 d is flattened, whichfacilitates soldering core support 111 cw to coil 110 c and providesflexibility at the tip of the guidewire 110 for atraumatic interactionwith tissue. The length of flattened section 1130 d can be about twocentimeters, for example. Dual core support designs have an advantage,relative to single core designs, of leaving openings in thecross-section of the guidewire for routing illumination fibers whilekeeping the overall outside diameter of the guidewire less than or equalto a desired maximum outside diameter.

FIGS. 21C-21D illustrate a variation of the core support 110 cw shown inFIG. 21A, in which FIG. 21C shows the core support 110 cw in the sameorientation as the one shown in FIG. 21A, while FIG. 21D shows the coresupport of FIG. 21C having been rotated by ninety degrees about thelongitudinal axis. In the example of FIGS. 21C-21D, wire 1130, proximalof the flattened distal end portion 1130 d and distal of the ungroundproximal portion 1130 p has been ground to provide multiple sections ofvarying diameter that decrease in a direction from proximal portion 1130p to distal portion 1130 d to form a tapering effect.

Alternative to the use of two core supports 110 cw and 111 cw, a singlecore support may be used, as already noted above with regard to FIG. 19.Further alternatively, such a single core support 110 cw can be madefrom an oval-shaped or elliptical-shaped (in cross-section) core wire ifenough space is available, which may be made available by eliminatingone of the illumination fibers 110 i, for example. FIG. 22A shows anexample of a core support 110 cw formed from an oval wire and FIG. 22Billustrates a proximal end view of core support 110 cw, showing the ovalprofile at the proximal end of core support 110 cw. Proximal portion1130 p of core support 110 cw is maintained as the full wire profilehaving the oval-shaped cross-section, wherein the height 1130 h of thewire is about 0.015″ and the width 1130 w of the wire is about 0.010″,see FIG. 22B. Intermediate section 1130 i is ground down to a roundcross-section having a diameter of about 0.010″ for greater flexibilityin a distal end portion of the guidewire 110. Distal end portion 1130 dis flattened, and may have a length of about 0.2 cm to about 1.2 cm, forexample, typically about 1 cm, which facilitates soldering core support110 cw to coil 110 c. The length of flattened section 1130 d ismaintained small, e.g., about 0.8 cm to prevent guidewire whipping.Alternatively, flattened section 1130 d may be eliminated altogetherwith the reduced diameter round cross section 11301 extending to thedistal end of core support 110 cw. The length of the section 1130 i(whether or not flattened section 1130 d is employed) may be varied tocustomize the length of a flexible distal end portion of guidewire 110.The dimensions of the oval or elliptical cross section may be varieddepending upon the amount of space available inside coil 110 c,accounting for all other components to be contained therein, as well asperformance characteristics (e.g., flexibility, stiffness, torquability,etc) desired.

Coil 110 c may be overlaminated, such as by melting nylon (or otherpolymer, such as PEBAX, GRILLAMID (nylon resin), or other medical graderesin) into open-pitched areas of the coil 110 c to fill in these areas.The overlamination material increases the steerability of guidewire 110,increases torquability of guidewire 110 and provides an area that can beeasily gripped by the user.

FIGS. 23A-31 are now referred to in describing manufacturing steps thatmay be carried out during the manufacture of certain embodiments ofilluminating guidewire 110. In these embodiments, coil 110 c extendsover substantially the entire length of guidewire 110 and at least oneof core supports 110 cw and 111 cw extends into a proximal portion ofguidewire 110. In FIG. 23A, a distal portion of coil 110 c is stretchedto break tension between adjacent coils and to form an open-pitchportion 110 co of coil 110 c to provide greater flexibility or“floppiness” in this portion, relative to the remainder of the coil nothaving been stretched. Next, two mandrels 1132 (which may be coated witha lubricious material such as polytetrafluoroethylene, or the like),having dimensions about the same as illumination fibers 110 i that willlater replace them, are inserted into coil 110 c, as illustrated in thelongitudinal sectional schematic of FIG. 23B. The core support 111 cwhaving the smaller cross-sectional proximal portion dimension (e.g.,core support 111 cw formed from a 0.006″ core wire, as described withregard to FIG. 21B above), referred to here as the “first core support”111 cw, is inserted into the coil 110 c such that a distal end of distalportion 1130 d is set back proximally from a distal end of coil 10 c bya predetermined distance. In one example, this predetermined distance isabout seven cm. In another example this predetermined distance is aboutnine cm. However, this predetermined distance may be varied dependingupon the desired performance characteristics of the distal end portionof illuminating guidewire 110. By decreasing the predetermined distance,this increases the stiffness, or moves the stiff section more distal onthe distal end portion of the guidewire 110. Increasing thepredetermined distance moves the stiff section more proximal and leavesa greater flexible length at the distal end portion of the guidewire110.

A third mandrel 1132, which may be made the same as the above-describedmandrels 1132, but which has dimensions to occupy a space that willlater be occupied by the second core support 110 cw, is inserted, whichappears as the bottom mandrel 1132 shown in FIG. 23B. FIG. 23C shows across-sectional view of this arrangement, with the bottom mandrel 1132being the mandrel that occupies the space that will be later filled bythe second core support 110 cw, and the other two mandrels 1132occupying the spaces that will be later filled by illumination fibers110 i. The distal end 1130 d of the core support 111 cw may then besoldered to coil 110 c.

In cases such as this, where coil 110 c is stainless steel and coresupport is made of a nickel-titanium alloy, oxide on the nickel-titaniummaterial, in regions to be soldered can be removed, prior to soldering,to improve solder joint strength. This removal can be accomplished usinga highly acidic flux. For example, a phosphoric acid-based flux (about65% to about 75%, by weight, phosphoric acid) was found to achievesatisfactory removal of the oxide. To further improve the solder jointstrength, the regions on the nickel-titanium material that are to besoldered can be manually cleared of oxide, such as by removal usingsandpaper or grinding. Further alternatively, or additionally, achemical etch may be used.

One example of a solder used to form the solder joints is a tin/silvereutectic solder (96.5% Sn, 3.5% Ag, 0.5% Cu). This eutectic alloy workswell as the solder in this case because strength is desired, and theeutectic alloy has no liquidus/solidus transition range, so the solderjoint solidifies all at once, which greatly reduces the chances, makingit almost impossible for the joint to be disrupted as it is solidifying.

Next, the mandrel 1132 occupying the space for the second core support110 cw is removed and the second core support 110 cw (e.g., core support110 cw formed from a 0.008″ core wire, as described with regard to FIG.21A above, referred to here as the “second core support” 110 cw) isinserted into the coil 110 c in the opening left by removal of themandrel 1132. The first and second core supports 111 cw and 110 cw arethen soldered to coil 10 c at multiple locations over the length of thecore supports. In one particular example, soldering of the second coresupport 110 cw includes a distal-most solder joint made about two toabout five coils back from a distal end of coil 110 c, a second solderjoint is made about two cm distal of the location along coil 10 c wherethe distal solder joint for the first core support 111 cw was made, athird solder joint is made proximal of the distal solder joint of thefirst core support, but distal of the transition between the open-pitchcoil section 110 co and the remainder of the coil 110 c (closed-pitchsection), a fourth solder joint is made proximal of the open-pitch coilsection 110 co, and a fifth solder joint is made at the proximal end ofcoil 110 c. The third, fourth and fifth solder joint locations join bothof the core supports 111 cw and 110 cw to the coil 10 c for addedstrength and rigidity.

By making the solder joint for the distal end of the first core support111 cw and the second solder joint of the second core support 110 cw atlocations on coil 10 c that are at unequal locations along thelongitudinal dimension of coil 110 c, this allows the core supports 111cw and 110 cw to slide independently of each other during bending of thedistal end portion of the illumination guidewire 110. For example, FIGS.24A and 24B illustrate this independent sliding capability. As shown,the distal end solder joint 1136 of the smaller core support 111 cw(core support 111 cw formed from the 0.006″ wire described in theexample above) is illustrated at the bottom of coil 110 c, the solderjoint 1134 just distal of solder joint 1136 made between the second coresupport 110 cw and coil 110 c is shown at the top side of theillustration, and both core supports 111 cw and 110 cw are soldered tocoil 10 c at a location distal of the transition between the open-pitchcoil section 110 co and the closed-pitch section, in this case, aboutsixteen cm from the distal end of coil 110 c. FIG. 24A shows therelative positions of the solder joints when coil 110 c is in a straightconfiguration. FIG. 24B shows coil 110 c in a bent configuration, andillustrates the ability of the core supports 111 cw and 110 cw to slideindependently of one another, as it can be observed that the solderjoints 1134 and 1136 have moved closer together, as compared to thespace between these joints shown in FIG. 24A when coil 110 c isstraight. Thus, when bending toward the first core support 111 c w, thefirst core support 111 cw is allowed to slide distally in relation tothe second core support 110 cw at the bend, because the cores arelocated together (same longitudinal fix point) at solder joints 1138,and the first core support 111 cw does not extend all the way to thedistal end of the coil 110 c. If the solder joints 1134 and 1136 of thetwo core supports 111 cw and 110 cw were soldered at the samelongitudinal location, this would make the arrangement much stiffer andless flexible in this region. This would also result in greater amountsof “whip” upon torquing the device.

By soldering the core supports 111 cw and 110 cw at locations 1134 and1136 as shown in FIGS. 24A-24B and described above, the coils of coil110 c are prevented from substantial separation even when coil 110 c isbent. This greatly increases the stiffness of guidewire 110/coil 110 cin a segment between the solder joints 1134 and 1138, but still allows adistal section (distal of joint 1134 to the distal solder joint of thesecond core support 110 cw) to remain floppy. Alternatively, to furtherincrease the stiffness of the region between joints 1134 and 1138, thecoils between joints 1134 and 1138 or between 1136 and 1138, or between1134 and 1136 can be placed under compression during the soldering ofthe joints.

Further alternative soldering arrangements include, but are not limitedto: soldering both core supports 111 cw and 110 cw at the distal end ofcoil 110 c. This increases the distal stiffness of the coil 110c/guidewire 110 and thus also reduces distal flexibility. This may alsogreatly increase whipping of the distal end when torquing theilluminating guidewire 110.

Further alternatively, the solder locations (locations longitudinallyalong the coil 110 c) can be varied. For example, by moving joints 1134and 1136 distally with respect to coil 110 c, but keeping the sameseparation distance between coils 1134 and 1136, this moves the stiffsection between the joints 1134 and 1136 closer to the distal end ofguidewire 110, reducing the flexible section at the distal end portionof guidewire 110. Conversely, moving joints 1134 and 1136 proximallywith respect to coil 110 c, but keeping the same separation distancebetween coils 1134 and 1136, moves the stiff section between the joints1134 and 1136 further from the distal end of guidewire 110, increasingthe length of the flexible section at the distal end portion ofguidewire 110 and reducing the length of the stiff section.

FIG. 25A illustrates an embodiment of an illuminating guidewire 110 inproduction showing solder joints employed in this embodiment. As notedabove, solder joint 1136 is made first to solder the first core support111 cw to coil 10 c. This solder joint is typically made while themandrel 1132 that occupies the space for the second core support 110 cwis still in place within the coil, to ensure that solder joint 1136 doesnot solder the second core support 110 cw to coil 110 c. In theembodiment shown in FIG. 25A, solder joint 1136 was made at a length ofabout eight cm from the distal end of coil 110 c, although this lengthmay vary in other embodiments, as noted above. The mandrel occupying thespace for the second core support 110 cw was a Teflon-coated mandrelhaving an outside diameter of about 0.0075″.

After making the solder joint 1136, the mandrel 1132 occupying the spacefor the second core support 110 cw can be removed and the second coresupport 110 cw is then inserted in its place within the coil 110 c. Thedistal solder joint 1134 can then be performed to solder the second coresupport 110 cw to coil 110 c in the location shown, and the remainingsolder joints 1138, 1139, and 1141 can be performed to solder both coresupports 111 w and 110 cw to the coil 110 c in the locations shown.

FIG. 25B is a longitudinal sectional view of the guidewire 110 of FIG.25A taken along line 25B-25B. This view more clearly shows the solderjoint 1134 to the more distally extending core support (second coresupport) 110 cw as well as solder joint 1138 to solder the first coresupport 111 cw to coil 110 c. FIG. 25C is an enlarged view of theportion of FIG. 25A surrounded by line 25C. This enlarged view moreclearly shows the solder joint 1134 that solders the second core support110 cw to coil 110 c and also shows the distal end of the second coresupport 110 cw extending distally of the distal end of coil 110 c by adistance 25 x. For example, distance 25 x may be in the range of about0.005 to about 0.015 inches. FIG. 25D is an enlarged view of the portionof FIG. 25B surrounded by line 25D, to more clearly show the solderjoint 1136 connecting the first core support member 111 cw (top coresupport member in FIG. 25D) to coil 110 c.

Once core supports 111 cw and 110 cw have been soldered to coil 110 caccording to any of the techniques described above, the open-pitch coilsection 110 co of coil 110 c can next be laminated. A nylon (or othermeltable polymer) tube 1140 is slid over the open-pitched coil section110 co, as illustrated in FIG. 26, and then a FEP (fluorinated ethylenepropylene) heat shrink tube 1142 is slid over the meltable polymer tube1140. Tubing 1142 is heated until it shrinks down around the coils ofthe open coil section 110 co and melts the polymer tubing into thespaces between the coils. After cooling, the shrink tubing 1142 isremoved.

FIGS. 27A-27B illustrate steps that may be performed to installconnector 1120 to the proximal end of guidewire 110. These steps may beperformed while at least the mandrels 1132 that are to be replaced byillumination fibers 110 i are still inserted through coil 110 c. A heatshrink tube (e.g., FEP heat shrink material) 1140 is shrunk down arounda proximal end portion of coil 110 c as illustrated in FIG. 26A whichshows a longitudinal sectional view of the heat shrink tubing, and aplan view of coil 110 c and mandrels 1132. The tubing 1142 extendsproximally beyond the proximal end of coil 110 c by a predetermineddistance, e.g. about two mm. Mandrels 112 act to keep the proximal endof tubing 1142 from shrinking closed during heating.

Next, connector 1120 is slid over tubing 1142 so as to substantiallyalign the proximal end of connector 1120 with the proximal end of tubing1142, as illustrated. Tubing 1142 help to center coil 110 c within theconnector 1120 and also functions as a strain relief. Adhesive 1144 canbe applied to adhere connector 1120 to tubing 1142. Another shrinktubing 1146 (e.g., polyeolefin shrink tubing) is slid over the distalend portion 1120 d of connector 1120 and shrunk down around the distalend portion 1120 d, tubing 1142 and coil 110 c, thereby securingconnector 1120 to coil 110 c and also functioning as a strain relief.Connector 1120 may include a rotatable (relative to coil 110) ornon-rotatable female luer connector, or rotatable (relative to coil 110)or non-rotatable male luer connector, for example.

At this time, the remaining mandrels 1132 can be removed from coil 110 cin preparation for installation of the light (illumination) fibers 110i. After removal of the mandrels 1132, two light fibers 110 i areinstalled in their place and extended distally beyond the distal end ofcoil 110 c. The illumination fibers 110 i are then cut to extend apredetermined distance distally of the distal end of coil 110 c. In oneexample, this predetermined distance is about 0.5 mm, although thispredetermined distance may vary. An adhesive lens 110 s is then formedby applying ultra-violet curable adhesive (or other transparent ortranslucent adhesive) over the portions of illumination fibers extendingdistally from the distal end of coil 110 c to completely encapsulatethese fiber portions, as shown in FIG. 28. Note that, for simplicity ofillustration, core supports have not been shown in the illustration ofFIG. 28, however, these would, of course, also be contained within thecoil 110 c. Adhesive lens 110 s will typically be formed to have ahemispherical distal surface, as shown, although the curvature and shapeof this distal surface can be varied, depending upon the characteristicsof light patterns desired to be emitted therefrom. Note that adhesive isalso applied so as to spread over at least one coil of the coil 110 cand at least one space between coils. Adhesive lens 110 s is then curedto complete the formation of the adhesive lens 110 s.

The same or a similar adhesive can be used to apply to the proximal endportion of coil 110 c and portions of the illumination fibers 110 i inthe proximal end 110 ps vicinity, as illustrated in FIG. 29. Adhesivecan be applied in amounts enough attach/encapsulate up to about one-halfof the proximally exposed portions of illuminating fibers 110 i thatextend proximally from the proximal end of coil 110 c. The illuminationfibers are then cut substantially flush with the proximal end ofconnector 1120, as shown in FIG. 29. Optionally, after curing theadhesive, the portion of shrink tubing 1142 extending proximally fromthe proximal end of coil 110 c, may next be shrunk down around theproximally extending portions of illumination fibers 110 i, for example,to an outside diameter of about 0.022″, to lower the light input intodevice 110 and allow light input substantially only through theillumination fibers 110 i. Alternatively, and also optionally, a grommet1148 (shown in phantom) can be inserted over illumination fibers andinside of shrink tubing 1142, with or without subsequent furthershrinking of the shrink tubing, to accomplish the same function.

Further optionally, the proximally extending portions of light fibers110 i may be completely encapsulated in adhesive or epoxy, in the samemanner as described above with regard to adhesive lens 110 s. Thisproximal adhesive lens 110 sp can be configured to function as a lens todirect light into light fibers 110 i, for example, but the adhesive orepoxy used in this instance must be able to withstand heat generated bythe light cable when connected to connector 1120 during use.

FIG. 30 shows an embodiment of an illuminating guidewire 110, butwithout connector 1120. In this embodiment, the more distally extendingcore support 110 cw, also referred to above as the second core support110 cw extends distally of the distal end of coil 110 c by about 0.005″to about 0.015″ (about one to two coil widths). The illumination fibers110 i extend distally beyond the distal end of coil 110 c by about0.010″ to about 0.020″, and the distal adhesive lens 110 s covers theprotruding distal end portion of the second core support 111 cw as wellas the protruding distal end portions of the illumination fibers 110 i.A stiff grip region 110 sr may optionally be provided by anoverlamination (of a type described above, such as heat shrink tubing,or the like) to act as a strain relief, although it is not necessary.Proximal adhesive lens 110 sp is also shown.

FIG. 31 illustrates an example of a permanently attached rotating maleluer connector 1120 that is attached to a proximal end portion ofilluminating guidewire 110 and is rotatable with respect thereto. Onenon-limiting example of a rotatable connector 1120 that may be used isQuosina Rotating Male Luer 71632 (Quosina Corp., Edgewood, N.Y.). Byproviding connector 120 as a permanently attached connector to device110, this ensures permanent alignment of the proximal lens 110 sp withthe proximal interface of the light source and thereby ensures alignmentof the light transmitted through the proximal lens 110 sp.Alternatively, a rotatable male luer connector 1120 or other connector1120 may be made detachable from the illuminating guidewire 110.Advantages to a removable or detachable arrangement include, but are notlimited to: allowing a balloon catheter or other tool or instrument tobe guided over guidewire 110 to be loaded from the proximal end of theilluminating guidewire 110; allowing illuminating guidewire 110 to besuccessfully inserted into a target sinus before even opening thepackaging of one or more tools, devices or instruments to be deliveredthereover; and exchanging tools, devices or instruments on theillumination guidewire 110 without having to remove the illuminationguidewire from the target surgical site and reinserting after exchange.

FIG. 32 shows the illumination guidewire 110 of FIG. 30 with connector1120 permanently connected thereto so that connector 1120 is rotatablewith respect to the flexible coil portion 110 c of the device 110. Inone non-limiting, exemplary embodiment, a distal end portion of device110 is coated with silicone to reduce friction against the inner surfaceof the irrigation catheter 10 in use. In the example shown in FIG. 32, alength 1145 of about 16±1 cm, starting from the distal tip of device110, is coated with silicone. As noted, this is a non-limiting example,as greater or lesser lengths may be coated with silicone. Furtheralternatively, the silicone coating may be eliminated altogether. In theexample shown in FIG. 32, the length 1147 of device 110 from the distaltip to the distal end of shrink tubing 1142 is about 95 cm and theoverall length 1149 of the device 110 is about 100 cm. Of course, thepresent invention is not limited to these lengths, as length 1147, aswell as length 1149 may be greater or less than that described in theexample of FIG. 32. In FIG. 32, tubing 1142 is 3/64″ polyolefin shrinktubing and tubing 1146 is ¼′ polyolefin shrink tubing, although thepresent invention is neither limited to these sizes nor materials. Thestiffened region 110 sr is formed by melting a nylon tube into theregion shown in a manner described above with regard to melting a nylontube into the stretched region 110 co. This tubing may be colored foreasy visualization. In the example shown, the nylon tubing is purple.Core wires 110 cw and 111 cw in this example are made of Nitinol, coil110 c is made of stainless steel and snag solder 1143 (i.e., soldercomprising tin and silver). Distal lens 110 s is made of UV Adhesive 204(Dymax Corporation, Torrington, Conn.).

Optionally, illuminating guidewire may be manufactured to have a presetcurve or bend in a distal end portion thereof. For example, the largercore support 110 cw in the process described above can be set with acurve or bend to form a resulting bend in the distal end portion ofguidewire 110 once constructed. FIG. 33A is a partial view of the coresupport 110 cw described with regard to FIG. 21A, while still in astraight configuration. FIG. 33B illustrates one method of forming apreset curve in core support 110 cw or 111 cw in which the flatteddistal end section 1130 d is bent at an angle of about ninety degrees bybending it around a mandrel 1150. In one example, mandrel 50 had aoutside diameter of about 0.05″. By cold working (i.e., plasticallydeforming) the distal portion about the mandrel 1150 and setting it aabout ninety degrees, a curve of about twenty degrees will result in thefinished illuminating guidewire device 110 employing this core supportin a manner as described above. Alternatively, the nickel-titaniumdistal end portion 1130 d can be bent in the same manner as shown inFIG. 33B, but rather than cold working, the distal end portion can beheated to its annealing temperature and then bent around the mandrel1150 and quenched.

FIG. 34 illustrates a distal portion of an illuminating guidewire 110manufactured with a core support have a preset bend from either of thetechniques described above with regard to FIGS. 33A-33B. The bend in thedistal end portion makes it more steerable, as discussed above and inapplication Ser. No. 11/647,530.

FIG. 35 is a partial view of coil 110 c illustrating two portions ofcoil 110 c that have been etched 10 e. Etching may be performed overall, or one or more select portions of coil 110 c to lower reflectanceof the coil where etched, such as when viewed by endoscopy, for example,and/or to act as a marker band to identify a particular location alongthe coil 110 c.

As noted above, all or a portion of illumination guidewire 110 may beexternally coated with a silicone coating to reduce friction (addlubricity) between guidewire 110 and the tissues, guides and/or otherinstruments that it is slid against during use. Other lubriciouscoatings may be substituted, including, but not limited to:polytetrafluoroethylene, parylene, hydrophilic coatings, any of whichmay be spray coated or dipped, for example, or may be pre-coated on thewire from which the coil is made by the wire manufacturer, or may bepre-coated on the coil 10 c if the coil is manufactured by an outsidesource.

The illumination fibers 110 i, as noted previously, can be free to moveabout radially within the device 110. Further, there is no need tocenter the illumination fibers 110 i with respect to device 110 even atthe distal and proximal ends of the device. The plastic or glassillumination fibers 110 i are typically used to transmit light from alight source such as one provided in an operating room for use byendoscopes, e.g., xenon light source, halogen light source, metal halidelight source, etc. Alternatively, device 110 may be configured totransmit light from other light sources, such as a laser light source,wherein laser fibers would be substituted for the illumination fibersdescribed above, and extend through device 110 in a fiber optic bundle.The fiber optic bundle, like the illumination fibers 110 i, contributesto stiffness (in both bending and torquing motions) of device 110,thereby enhancing trackability, steering and other torquing.Alternatively, device 110 may employ one or more light emitting diodesused to emit light, as described in more detail in application Ser. No.11/647,530.

A light cable 1032 optically connects connector 1120 with light source1030 to deliver light from the light source 1030 through connector 1120and illumination fibers 110 i. The light cable 1032 must transmit enoughlight to allow the illuminating guidewire 110 to transilluminate thesinuses, but at the same time, not transmit so much light that the lightfibers become damaged. Research has shown that very bright light sources1030 (e.g., 300 Watt Xenon, new bulb) can damage the light fibers 110 iwith a light cable surrounding a glass illumination fiber bundle whereinthe light cable has a diameter of greater than about 2 mm. One way toconcentrate the light coming from light cable 1032 down to a size morenearly matching that needed for the illumination fibers 110 i is toprovide a taper (which may be made of glass, for example) 1126 asillustrated in phantom in FIG. 36. For example, taper 1126 may taper thediameter of the incoming light from about 2 mm down to about 1 mm. Whilethe taper 1032 can concentrate or focus the light down, as noted, thereare light losses that result in heat generation at the location of thetaper 1126.

Alternatively, a light cable 1032, in this embodiment, has a connector1320 at the distal end of light cable 1032 which is provided with a maleluer 1322, for connection to the connector 1120 of illuminationguidewire 110. The provision of a male luer is non-standard, as mostoperating room light cables are provided connectors specific to themanufacturer of the light cable, which are often proprietary to thatmanufacturer and which do not include a luer connector. Accordingly,when the connector 1120 of illuminating guidewire 110 is configured tomate with this male luer 1322, this prevents a standard operating roomlight cable from accidentally being connected to the guidewire 110. Thelight fiber bundle in light cable 1032 is sized to provide sufficientillumination through illuminating guidewire 110 to transilluminate thesinuses, but an insufficient amount of light to damage the illuminationfibers 110 i. Also, a taper 1026 is not required since the light cable1032 is sized to substantially match the illumination fibers 110 i, andtherefore the heat generation problem caused by tapering does not arisewith this embodiment. In one example, the light fiber bundle 1324 has adiameter of about 1 mm.

Alternatively, the embodiment shown in FIG. 37 may also be provided witha taper 1126 to further funnel the light from light bundle 1324 down toa smaller diameter, as illustrated in FIG. 38.

FIG. 39 shows connector 1320 of light cable 1302 provided with a femaleluer mated with a male luer of connector 1120 of the illuminatingguidewire 110. This arrangement allows the proximal ends of illuminationfibers 110 i to be placed flush in abutment with the light bundle 1324or taper 1126 (as shown) when connector 1120 is screwed or snapped ontoconnector 1320.

Any of the devices 110 described herein may optionally include one ormore radiopaque markers and/or electromagnetic coils on the tip of thedevice 110 and/or elsewhere along the device for enhancing visibility byfluoroscopy systems, image guided surgery (IGS) systems, or othervisualization systems.

FIG. 40 shows an alternative design of device 110 in which light isemitted proximally of the distal end of the device. This configurationmay employ any of the various light transmission means described above(e.g., illumination fibers, laser fibers, LED). The proximal portion 110p may be constructed in any of the manners described above with regardto other embodiments of device 110. The distal portion 110 d includes atransparent proximal end portion 110 dp that mounts over the distal endof proximal end portion 110 p of the device 110. The transparent portion110 dp permits the illumination emitted from illumination member 110 ior 110 id to pass out of the device 110 at the location of transparentportion 110 dp. The illumination member(s) 110 i or 110 id thusterminate at the proximal end portion 110 dp of the distal end portionof device 110. Distally of this transparent portion 110 dp, the distalportion 110 dd of distal end portion 110 d of device 110 extends as afloppy guidewire leader or tip. This floppy guidewire leader or tip 110dd may include a coiled section 110 c and may optionally include a coresupport 110 cw/111 cw. The light emitted from illumination fibers willdisperse naturally through the transparent portion 110 dp. Optionally, adeflector 111, such as a convex mirror (e.g., parabolic or other convex)shape or other reflective surface may be provided distally ofillumination fibers/light emitting portion 110 i, 110 id of device 110to deflect light rays out of the transparent portion. Additionally, orfurther alternatively, illumination fibers 110 i may be angled at thedistal end portions thereof to direct the emitted light out through thetransparent portion.

This configuration may be beneficial in further protecting theillumination emitter(s) 110 i from foreign materials inside the body, aswell as from trauma that may be induced by bumping the illuminationemitter up against structures within the body. Further, a floppyguidewire leader 110 dd of this type may provide more flexibility andmaneuverability than a device in which the illumination emitter islocated on the distal tip of the device.

Transparent portion 110 dp may be provided as a clear plastic or glassintegral tube, or may have openings or windows 110 t provided therein(see the partial view of FIG. 41). Further alternatively, transparentportion may be formed by a plurality of struts 110 st circumferentiallyarranged to interconnect the distal floppy tip 110 dd with the proximalend portion 110 p of device 110 as shown in the partial illustration ofFIG. 42. Alternatively members 110 st may be intersecting in acriss-crossing cage like configuration or other cage configuration. Inany of these alternative configurations, members 110 st may betransparent, but need not be and could be formed of non-transparentmaterials, such as metals or opaque plastics, for example.

Turning now to FIGS. 43A-43C, illustrations of partial coronal sectionalviews through a human head showing various steps of a method forinserting an illuminating guidewire 110 into an ostium that opens to afrontal sinus are shown. The methods described here, and all othermethods disclosed herein may also comprise a step of cleaning orlavaging anatomy within the nose, paranasal sinus, nasopharynx or nearbystructures including but not limited to irrigating and suctioning. Thestep of cleaning the target anatomy can be performed before and/or aftera diagnostic or therapeutic procedure. The methods of the presentinvention may also include one or more preparatory steps for preparingthe nose, paranasal sinus, nasopharynx or nearby structures for theprocedure, such as spraying or ravaging with a vasoconstricting agent(e.g., 0.025-0.5% phenylephyrine or Oxymetazoline hydrochloride(Neosynephrine or Afrin) to cause shrinkage of the nasal tissues, anantibacterial agent (e.g., provodine iodine (Betadine), etc. to cleansethe tissues, etc.

In FIG. 43A, a first introducing device in the form of a sinus guide 12is introduced through a nostril and through a nasal cavity 1012 to alocation close to an ostium 1034 of a frontal sinus 1036. Sinus guide 12may be as described previously herein, or as described in theapplications incorporated herein by reference. The advancement of sinusguide 12 can be visualized with a scope inserted into the nasal cavity1012 (e.g., through channel 28, not shown in FIG. 43A) and advanced asclose to the ostium 1034 as possible without causing significant traumato the tissues therein.

Once the surgeon is satisfied that the distal end of the sinus guide 12is positioned close enough to the appropriate ostium 1034, illuminatingguidewire 110, connected to a light source as described by any of thetechniques mentioned above, is inserted through sinus guide 12 andadvanced therethrough, see FIG. 43B. There may be some transilluminationfrom the light emitted from the scope which can be used to confirm thatthe sinus guide 12 is positioned in the correct general area, whichconfirmation can be made even before the distal tip of guidewire 110exits the distal end of sinus guide 12. However, much more specifictransillumination effects are produced when the tip of guidewire 110exits the distal end of guide 12 and especially when the light emittingportion of guidewire 110 touches or approximates an intended targetsurface, such as an inner wall of a sinus, for example. As the guidewire110 is advanced, transillumination on the face of the patient can beobserved as a glowing spot that moves as the distal end portion ofdevice 110 moves, thereby making it possible to visibly track thelocation of the light emitting portion of device 110 without the need touse radiographic imaging, such as by fluoroscopy, for example.

While there may be some diffuse transillumination on the forehead of thepatient overlying the frontal sinus 1036 as the light emitting portionof device 110 approaches the ostium 1034, the glow on the foreheadbecomes brighter and smaller in dimension (more focused) as the lightemitting portion passes through the ostium 1034 and enters the frontalsinus 1036, FIG. 43C. As device 110 is further advanced, the glowingspot becomes most defined and brightest as the light emitting portionapproaches and contacts a wall of the frontal sinus 1036. Further, asnoted, the movement of the transilluminated spot can be visibly followedto confirm that the guidewire 110 is indeed moving within the locationof the frontal sinus, as can be confirmed by the surgeon's knowledge ofthe particular anatomy of the patient being treated. In this regard, aCAT scan or other image of the sinus anatomy can be performed prior tothis procedure and studied by the surgeon, to apprise the surgeon of anydistinctive or unusual patterns in the individual patient's sinusanatomy which might be useful in tracking and confirmation of where theguidewire is located, as indicated by the transillumination.

Illuminating guidewire device 110 can also be used to facilitatevisualization and placement of the sinus guide 12 in the proceduredescribed above with regard to FIGS. 43A-43C, or in another procedure inwhich a sinus guide, sinus guide or guide tube is placed in the sinuspathways. FIG. 44 illustrates a situation where scope 30 has beeninserted as far as possible without causing significant trauma to thepatient. The range of visibility in this case does not extend all theway to ostium 1034, as indicated schematically by the rays 1009 shownextending distally from scope 30. By inserting illuminating guidewire110 through sinus guide 12 (tube 44) as shown in FIG. 44, additionalillumination can be provided distally of the illuminating range of scope30. This additional illumination can be received by scope 30 to enablevisualization up to the illumination portion of device 110 andpotentially even extending to illumination range of device 110, as longas there is a straight pathway of the field of view. Thus, placement ofthe guidewire 110 can be visualized up to and into the desired ostium1034 via scope 30 in this case. Alternatively, this can be carried outwithout the sinus guide 12, wherein the guidewire 110 is inserted andthe scope 30 can be used to visualize placement of guidewire 110 intothe target ostium with the assistance of the light emitted by the scope30 in addition to the light emitted by guidewire 110.

In any of these procedures where a scope 30 is used for visualizationand an illuminating guidewire 110 is inserted, some transillumination ofthe target sinus may occur from the light emitted by the scope 30 alone.However, this transillumination will be diffuse and show a rather dim,large area of transillumination on the patient's skin. When theillumination guidewire 110 is inserted and advanced, as noted earlier, asmaller, brighter transillumination spot will be visible when theilluminating portion of the guidewire has entered the sinus.Additionally, even before entering the sinus, the light emitted from theguidewire 110 will produce a moving transillumination spot as guidewire110 is advanced, which also helps distinguish the location of the distalportion of the guidewire 110, relative to any diffuse transilluminationproduced by the scope light.

If the guidewire 110 is advanced into an ostium other than the targetostium (e.g., ostium 1035 shown in FIG. 44), this may be possible to beviewed by scope 30, depending upon the line of sight. However, even ifit is not, the transillumination resulting from entrance into adifferent sinus than the target sinus will be evident by the differentlocation on the patient's face. Also, in the example shown, guidewire110 would not be able to be advanced very far through ostium 135 beforeit was diverted and curled by the relatively small sinus space thatostium 135 leads into. Thus, by tracking the movement of theillumination spot produced by guidewire 110, the surgeon could confirmthat guidewire 110 was misplaced as the guidewire would be diverted by amuch smaller space then that characterized by the target frontal sinus1036.

Thus, by using an illuminating guidewire device 110 in the methods asdescribed above, the use of fluoroscopy or other X-ray visualization canbe reduced as it is not required to confirm proper placement of theguidewire in some cases.

Another optional feature that guidewire 110 may be provided with is theability to emit strobed, flashing or flickering light, as described indetail in application Ser. No. 11/647,530. Additionally, oralternatively, the light emitted may have a different wavelength (i.e.,color) than light emitted by endoscope 30 or may be configured to changecolors over time. The transillumination produced by a flashing and/orcolored and/or color changing light can be further distinguished fromdiffuse transillumination produced by other light sources, such asendoscopes, for example, since the transillumination produced by theguidewire 110 in this case will flicker or vary in intensity betweenbright and dim and/or vary in color.

Guide Systems with Removable Endoscope/Guidewire Sheaths

FIGS. 45-47 show additional embodiments of transnasally insertable guidesystems useable to position an endoscope 30 at a desired location withinthe ear, nose, throat or cranium of a human or animal subject, to viewanatomy for diagnostic purposes or for confirmation that a procedure hasbeen successfully accomplished. In FIG. 45, guide device 12 includes asingle tube 28 having a lumen sized to receive endoscope 30. Guide 12may be preshaped to be straight or curved, or may be configured to bedeflectable or steerable.

FIGS. 46-47 illustrate a guide system comprising a straight or curvedtransnasal sinus guide 12 and a sheath 90 that is insertable through thesinus guide 12. The sheath 90 has a single lumen sized and configured toreceive endoscope 30 therethrough. Thus, endoscope 30 may be insertedthrough sheath 90 to extend distally of the distal end of guide 12, asillustrated in the partial view of FIG. 47, to view anatomy or visuallyverify the results of a procedure, for example. Examples of transnasalsinus guides 12 useable in this system include those described in U.S.patent application Ser. No. 11/193,020 and herein, as well as thosecurrently available commercially as Relieva™ Sinus Guide Catheters fromAcclarent, Inc., Menlo Park, Calif.

Sheath 90, illustrated in FIG. 46, includes an elongate flexible shaft92 through which the endoscope lumen 85 extends. A proximal hub 94 maybe provided with having two arms 96, 98, and is mounted on the proximalend of the flexible shaft 92. Arm 96 leads into the endoscope lumen 85and arm 98 also leads to the endoscope lumen 85 and can be used, forexample to attach a suction or irrigation source thereto. Alternatively,hub 94 may be provided with only a single arm 96.

It is to be appreciated that the invention has been described hereabovewith reference to certain examples or embodiments of the invention butthat various additions, deletions, alterations and modifications may bemade to these examples and embodiments and or equivalents may besubstituted without departing from the intended spirit and scope of theinvention. For example, any element or attribute of one embodiment orexample may be incorporated into or used with another embodiment orexample, unless to do so would render the embodiment or exampleunsuitable for its intended use. In addition, many modifications may bemade to adapt a particular situation, material, composition of matter,process, process step or steps, to the objective, spirit and scope ofthe present invention. All such modifications are intended to be withinthe scope of the claims appended hereto.

1-58. (canceled)
 59. An illuminating guidewire device comprising: aflexible distal end portion; at least one light emitting element in saiddistal end portion; at least one structure extending from a proximal endof said device through a proximal end portion of said device and atleast part of said distal end portion to connect said at least one lightemitting element with a power source; a coil; and at least one coilsupport within said coil, at least a portion of each said at least onecoil support fixed to said coil.
 60. The device of claim 59, whereinsaid device includes two of said coil supports.
 61. The device of claim60, wherein said coil supports are fixed to said coil at predeterminedlocations along lengths of said coil supports, at least one fixationlocation on a first of said coil supports being placed in a directionlongitudinally along said coil away from a longitudinal location of acorresponding fixation location on the other of said coil supports,thereby allowing said coil supports to slide relative to one anotherwhen said coil bends.
 62. A method of making an illuminating guidewire,said method comprising the steps of: providing a coil having apredetermined length and diameter; inserting mandrels through an annulusof the coil; inserting a first core support into the coil and fixing aportion of the first core support at a predetermined length from adistal end of the coil; removing a mandrel and inserting a second coresupport; fixing said second core support at predetermined locationsalong a length thereof, to the coil and fixing the first core support atadditional locations along the length thereof to the coil; and insertingillumination fibers. 63-65. (canceled)